US20100217378A1 - Stents With Profiles For Gripping A Balloon Catheter And Molds For Fabricating Stents - Google Patents

Stents With Profiles For Gripping A Balloon Catheter And Molds For Fabricating Stents Download PDF

Info

Publication number
US20100217378A1
US20100217378A1 US12/772,893 US77289310A US2010217378A1 US 20100217378 A1 US20100217378 A1 US 20100217378A1 US 77289310 A US77289310 A US 77289310A US 2010217378 A1 US2010217378 A1 US 2010217378A1
Authority
US
United States
Prior art keywords
stent
mold
bore
section
delivery system
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
US12/772,893
Other versions
US8393887B2 (en
Inventor
Daniel Gene Brown
Hector Onello Torres
Mark Harris
Chris Andrews
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to US12/772,893 priority Critical patent/US8393887B2/en
Publication of US20100217378A1 publication Critical patent/US20100217378A1/en
Priority to US13/794,128 priority patent/US20130197620A1/en
Application granted granted Critical
Publication of US8393887B2 publication Critical patent/US8393887B2/en
Expired - Fee Related legal-status Critical Current
Adjusted expiration legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/958Inflatable balloons for placing stents or stent-grafts
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/9522Means for mounting a stent or stent-graft onto or into a placement instrument
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/91533Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands

Definitions

  • This invention relates generally to stent delivery apparatuses, and more particularly, but not exclusively, to a stent for gripping a balloon catheter and a mold for fabricating the stent.
  • Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent.
  • Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of affected vessels.
  • stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at a desired location. Examples in the patent literature disclosing stents include U.S. Pat. No. 4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to Gianturco, and U.S. Pat. No. 4,886,062 issued to Wiktor.
  • stents are delivered to the desired location by crimping the stent tightly onto a balloon catheter and transporting the crimped stent/balloon catheter combination to the desired location through a patient's vasculature.
  • the balloon catheter is expanded to contact the inner diameter of the stent.
  • the balloon catheter is expanded, thereby expanding the stent to contact the inner diameter of the patient's artery.
  • the balloon catheter is then deflated and removed from the vasculature.
  • the stent Since the stent and catheter travel through the patient's vasculature, the stent must have a small diameter so that it can pass through small lumens of the patient's vasculature. Secure attachment to the catheter is desirable so that the stent does not prematurely detach from the catheter.
  • the stent should also be sufficiently flexibility to travel through curvatures in the patient's vasculature.
  • crimping techniques can be uneven, leading to sharp edges on the crimped stent that can damage or get caught on the patient's vasculature during delivery. Further, crimping can decrease flexibility of the stent, making it hard to deliver the stent through curvatures in the patient's vasculature.
  • the balloon catheter may cause excessive expansion of the stent, thereby making it hard to transport the stent through the patient's vasculature (e.g., cross tight lesions). Further, expansion of the balloon catheter can cause the distal and proximal ends of the stent to expand further than the rest of the stent, causing the distal and proximal ends to have upward tapered edges that can get caught in the patient's vasculature, thereby decreasing deliverability.
  • a stent comprises a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent, the tapered sections being adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.
  • a mold comprises a mold member having a projection into a proximal section of a mold bore of the mold member, the projection configured to mold a tapered section at a proximal end of a stent mounted on a delivery system, the tapered section adapted to improve the attachment of the stent to the delivery system and facilitate the delivery of the mounted stent into and through a bodily lumen.
  • a mold comprises a mold member comprising a mold bore configured to mold a stent mounted on a delivery system.
  • the mold bore has a proximal section tapering inward to a proximal end of the mold bore and a distal section tapering inward to a distal end of the mold bore.
  • the tapered sections are adapted to mold tapered sections of the stent that improve the attachment of the stent to the delivery system and that facilitate the delivery of the mounted stent into and through a bodily lumen.
  • FIG. 1 is an illustration of a stent.
  • FIG. 2 is a diagram illustrating a stent installed on a balloon catheter using the mold of FIG. 7 .
  • FIG. 3 is a diagram illustrating a stent formed using the mold of FIG. 9 .
  • FIG. 4 is a diagram illustrating a stent formed using the mold of FIG. 10 .
  • FIG. 5 is a diagram illustrating a stent formed using the mold of FIG. 11 .
  • FIG. 6 is a diagram illustrating a mold according to an embodiment of the invention.
  • FIG. 7 is a diagram illustrating a cross section of the mold of FIG. 6 .
  • FIG. 8 is a diagram illustrating a mold according to another embodiment of the invention.
  • FIG. 9 is a diagram illustrating a cross section of the mold of FIG. 8 .
  • FIG. 10 is a diagram illustrating a cross section of a mold according another embodiment of the invention.
  • FIG. 11 is a diagram illustrating a cross section of a mold according another embodiment of the invention.
  • FIG. 12 is a flowchart illustrating a method of gripping a stent on a catheter according to an embodiment of the invention.
  • the term “implantable medical device” is intended to include self-expandable stents, balloon-expandable stents, stent-grafts, and grafts.
  • the structural pattern of the device can be of virtually any design.
  • a stent for example, may include a pattern or network of interconnecting structural elements or struts.
  • FIG. 1 depicts an example of a three-dimensional view of a stent 10 .
  • the stent may have a pattern that includes a number of interconnecting elements or struts 15 .
  • the embodiments disclosed herein are not limited to stents or to the stent pattern illustrated in FIG. 1 .
  • the embodiments are easily applicable to other patterns and other devices.
  • the variations in the structure of patterns are virtually unlimited. As shown in FIG. 1 the geometry or shape of a stent varies throughout its structure.
  • a stent may be formed from a tube by laser cutting the pattern of struts in the tube.
  • the stent may also be formed by laser cutting a polymeric or metallic sheet, rolling the pattern into the shape of the cylindrical stent, and providing a longitudinal weld to form the stent.
  • Other methods of forming stents are well known and include chemically etching a sheet and rolling and then welding it to form the stent.
  • a polymeric or metallic wire may also be coiled to form the stent.
  • the stent may be formed by injection molding of a thermoplastic or reaction injection molding of a thermoset polymeric material. Filaments of the compounded polymer may be extruded or melt spun.
  • filaments can then be cut, formed into ring elements, welded closed, corrugated to form crowns, and then the crowns welded together by heat or solvent to form the stent.
  • hoops or rings may be cut from tubing stock, the tube elements stamped to form crowns, and the crowns connected by welding or laser fusion to form the stent.
  • an implantable medical device may be configured to degrade after implantation by fabricating the device either partially or completely from biodegradable polymers.
  • Polymers can be biostable, bioabsorbable, biodegradable, or bioerodable.
  • Biostable refers to polymers that are not biodegradable.
  • the terms biodegradable, bioabsorbable, and bioerodable, as well as degraded, eroded, and absorbed, are used interchangeably and refer to polymers that are capable of being completely eroded or absorbed when exposed to bodily fluids such as blood and can be gradually resorbed, absorbed, and/or eliminated by the body.
  • a biodegradable device may be intended to remain in the body for a duration of time until its intended function of, for example, maintaining vascular patency and/or drug delivery is accomplished.
  • vascular patency and/or drug delivery For biodegradable polymers used in coating applications, after the process of degradation, erosion, absorption, and/or resorption has been completed, no polymer will remain on the stent. In some embodiments, very negligible traces or residue may be left behind. The duration is typically in the range of six to twelve months.
  • polymers that may be used to fabricate embodiments of implantable medical devices disclosed herein include, but are not limited to, poly(N-acetylglucosamine)(Chitin), Chitosan, poly(3-hydroxyvalerate), poly(lactide-co-glycolide), poly(3-hydroxybutyrate), poly(4-hydroxybutyrate), poly(3-hydroxybutyrate-co-3-hydroxyvalerate), polyorthoester, polyanhydride, poly(glycolic acid), poly(glycolide), poly(L-lactic acid), poly(L-lactide), poly(D,L-lactic acid), poly(D,L-lactide), poly(L-lactide-co-D,L-lactide), poly(caprolactone), poly(L-lactide-co-caprolactone), poly(D,L-lactide-co-caprolactone), poly(glycolide-co-caprolactone), poly(trimethylene carbonate), polyester amide, poly(N
  • PEO/PLA polyphosphazenes
  • biomolecules such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid
  • polyurethanes silicones
  • polyesters polyolefins, polyisobutylene and ethylene-alphaolefin copolymers
  • acrylic polymers and copolymers other than polyacrylates vinyl halide polymers and copolymers (such as polyvinyl chloride), polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidene halides (such as polyvinylidene chloride), polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters (such as polyvinyl acetate), acrylonitrile-styrene copolymers, ABS resins, polyamides (such as Nylon 66 and polycaprolactam), polycarbonates, polyoxymethylenes, polyimides,
  • polymers that may be especially well suited for use in fabricating embodiments of implantable medical devices disclosed herein include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL), poly(butyl methacrylate), poly(vinylidene fluoride-co-hexafluoropropene) (e.g., SOLEF 21508, available from Solvay Solexis PVDF, Thorofare, N.J.), polyvinylidene fluoride (otherwise known as KYNAR, available from ATOFINA Chemicals, Philadelphia, Pa.), ethylene-vinyl acetate copolymers, poly(vinyl acetate), styrene-isobutylene-styrene triblock copolymers, and polyethylene glycol.
  • EVAL ethylene vinyl alcohol copolymer
  • poly(butyl methacrylate) poly(vinylidene fluoride-co-hexafluoropropene)
  • a device may be made of a metallic material or an alloy such as, but not limited to, cobalt chromium alloy (ELGILOY), stainless steel (316L), high nitrogen stainless steel, e.g., BIODUR 108, cobalt chrome alloy L-605, “MP35N,” “MP20N,” ELASTINITE (Nitinol), tantalum, nickel-titanium alloy, platinum-iridium alloy, gold, magnesium, or combinations thereof “MP35N” and “MP20N” are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co., Jenkintown, Pa. “MP35N” consists of 35% cobalt, 35% nickel, 20% chromium, and 10% molybdenum. “MP20N” consists of 50% cobalt, 20% nickel, 20% chromium, and 10% molybdenum.
  • ELGILOY cobalt chromium alloy
  • 316L stainless steel
  • high nitrogen stainless steel e
  • a small profile stent (crimped tightly) with a small stent diameter allows for secure attachment and eases transport through narrow lumen passages.
  • decreasing a profile of a stent also decreases flexibility of the stent.
  • a larger profile stent (expanded stent) with a large stent diameter allows for greater flexibility.
  • a large profile makes transport through narrow lumen passages more difficult.
  • the negative effects on delivery of a small and large profile can be reconciled by using a stent having both large and small profile sections.
  • the small profile sections facilitate secure attachment, while the large profile sections facilitate flexibility.
  • a small profile section at or proximate to a stent end that is a leading end or edge during delivery may be particularly helpful in facilitating delivery.
  • implantable medical devices such as stents, having at least these characteristic are disclosed herein.
  • an implantable medical device such as a radially expandable stent mounted on a delivery system may include a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent.
  • the tapered sections may be adapted to improve the attachment of the stent to the delivery system. Additionally, the tapered section may facilitate the delivery of the mounted device into and through a bodily lumen.
  • Facilitating delivery may include facilitating smooth communication of device through a lumen without substantially limiting the ability of device to bend around curvatures in the lumen.
  • Facilitating delivery also may include improving a grip or attachment of the device on the delivery system since.
  • a tapered portion of a device may tend to strengthen a grip of the device on the delivery system.
  • a tapered section may inhibit or prevent disengagement of the device from the delivery system.
  • At least a portion of the stent may have a cross-section that is circular or substantially circular.
  • a delivery system may be, for example, a balloon catheter for delivering a stent.
  • FIG. 2 depicts an axial cross section of a stent 220 having tapered sections 230 and 240 at a distal end and a proximal end, respectively.
  • Stent 220 may be installed on balloon catheter 210 using a mold 600 in FIG. 7 .
  • Installed stent 220 has a profile in which proximal section 230 and distal section 240 of stent 220 exhibit an inward taper, instead of straight or outward taper outwards, as with conventional stents.
  • stent 220 can more easily travel through a patient's vasculature during delivery and is less likely to get caught in or damage the vasculature. Further, since the majority of stent 220 has an expanded profile, stent 220 can still track curvatures in the vasculature.
  • the profile also causes stent 220 to “hug” or grip balloon catheter 210 , thereby increasing the ability of stent 220 to stay mounted to the balloon catheter during delivery (until balloon 210 is deflated).
  • an implantable medical device such as a stent mounted on a delivery system may have a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent.
  • the tapered sections may be adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.
  • a device may have profile that tapers inward relatively uniformly between the proximal section and the distal section.
  • the mounted stent may have an “arrow-like” shape.
  • FIG. 3 depicts a stent 300 having a proximal section 310 that is tapered inward toward a proximal end.
  • Stent 300 also has a section 320 that tapers inward relatively uniformly from the proximal section to a distal end to adopt an arrow-like shape.
  • Stent 300 may be installed on a balloon catheter using a mold 800 in FIG. 9 .
  • a small profile at a leading end or edge of a stent is particularly advantageous.
  • the distal end may be a leading edge during delivery.
  • a “leading edge” is the edge of stent that faces the direction of travel during implantation of the stent.
  • the proximal section may taper inward relatively uniformly from an intermediate point between the proximal end and the distal end to the proximal end.
  • the distal section may taper inward relatively uniformly from the intermediate point to the distal end.
  • FIG. 4 depicts a stent 410 having a proximal section 420 and a distal section 430 that taper inward relatively uniformly from an intermediate point 440 .
  • Stent 410 has a diameter that gradually increases from a minimum value at the proximal and distal ends to a maximum value at intermediate point 440 .
  • Intermediate point 440 may be approximately midway between the proximal and distal ends of the stent.
  • Stent 410 may be installed on a balloon catheter using a mold 1000 in FIG. 10 .
  • a diameter of a stent that is about 6 mm long and about 0.041 inches in diameter at its midpoint can have a diameter at the distal and proximal ends between about 0.037 inches to about 0.038 inches.
  • the profile of stents 220 , 300 , and 410 facilitate a firm attachment of the stents to a balloon catheter, while maintaining flexibility. Further, the stents may travel more easily through tight lumens due to the small diameter at the ends as compared to conventional stents. Further, the stents are less likely to get caught or damage the patient's vasculature because the stents lack upwardly tapered ends as conventional stents may have after balloon catheter expansion.
  • an implantable medical device such as a stent mounted on a delivery system may include a section having a cross-section that oscillates in size between a proximal section and a distal section.
  • the oscillating cross section may be adapted to improve flexibility during delivery of the mounted stent.
  • Such a stent may have a “wave-like” profile with peaks and troughs.
  • the section of a stent having a wave-like profile may have at least one narrow region alternating with at least one wide region. At least a portion of the at least one narrow region is in contact with a surface of the delivery system. In addition, at least a portion of the at least one wide region may not be in contact with the surface of the delivery system. Thus, narrow regions may allow the stent to grip a balloon catheter. In addition, the wide regions allow the stent to flex and bend as the mounted stent passes through curved and/or narrow vasculature.
  • FIG. 5 depicts a stent 520 with an oscillating cross section formed using mold 1100 in FIG. 11 .
  • Stent 520 has a wave-like shape or profile, which provides the advantages mentioned above. It will be appreciated by one of ordinary skill in the art that stent 520 can take other wave profiles. For example, the profile can include additional crests and troughs and/or can be symmetrical or asymmetrical.
  • a mold for implantable medical devices may include a mold member having a mold bore configured to mold a stent mounted on a delivery system.
  • the mold member may mold the stent after the delivery system expands an outer surface of the stent onto at least a portion of an inner surface that defines the mold bore.
  • a mold member may be composed of more than one piece.
  • the mold member may be composed of two halves. Each half may have a device-holding groove. The grooves may be configured to form the mold bore when the two halves are joined.
  • the mold may include a lock adapted to inhibit or prevent opening of the mold during molding of the device.
  • a mold member may have a projection into a proximal section of a mold bore of the mold member.
  • the projection may be configured to mold a tapered section at a proximal end of an implantable medical device, such as a stent, mounted on a delivery system.
  • the tapered section as described above, may be adapted to improve the attachment of the stent to the delivery system and facilitate the delivery of the mounted stent into and through a bodily lumen.
  • the mold member may have a second projection into a distal section of a mold bore of the mold member for molding a tapered section into a distal end of a stent.
  • the projection may include a cylindrical member having an annulus disposed within the mold.
  • FIG. 6 is a diagram illustrating a mold member or mold 600 according to an embodiment of the invention that may, for example, mold stent 220 in FIG. 2 .
  • Mold 600 takes a split mold shape and has two halves: 610 a and 610 b, each having a groove 620 a and 620 b, respectively, running down a longitudinal axis of halves 610 a and 610 b.
  • Halves 610 a and 610 b are coupled together via a hinge 615 that enables mold 600 to open and close via rotation of one half with respect to the other half. Hinge 615 ensures proper alignment of the halves 610 a and 610 b when mold 600 is closed.
  • Grooves 620 a and 620 b are configured to receive and hold a balloon catheter 210 ( FIG. 2 ) and a stent 220 ( FIG. 2 ) in place.
  • Grooves 620 a and 620 b form a mold bore 625 ( FIG. 7 ) through mold 600 when mold 600 is closed, that has a diameter greater than the diameter of stent 220 (e.g., from about 0.003 inches greater to about 0.048 inches greater for a stent which is approximately 0.045 inch in diameter).
  • Grooves 620 a and 620 b each include two half washers 650 spaced apart to approximately match the length of stent 220 .
  • Half washers 650 project or extend into grooves 620 a and 620 b.
  • balloon catheter 210 When balloon catheter 210 is expanded (via internal air pressure), balloon catheter 210 pushes against an inner surface of stent 220 , causing stent 220 to expand to match the diameter of bore 625 formed by grooves 620 a and 620 b. However, since half washers 650 extend into grooves 620 a and 620 b, the proximal and distal ends of stent 220 cannot expand to the same diameter as the rest of the stent 220 (e.g., to the diameter of bore 625 ).
  • stent 220 has a profile after molding in which at least a portion of its proximal and distal ends are tapered inwards.
  • the tapered inward edges facilitate smooth communication of stent 220 through a patient's vasculature without substantially limiting the ability of stent 220 to bend around curvatures in the vasculature.
  • the tapered ends tend to grip the balloon catheter 210 better than untapered ends, inhibiting or preventing stent 220 from disengaging from balloon catheter 210 before it is deflated.
  • Half 610 a includes a first member 630 of a barrel locking mechanism.
  • Half 610 b includes a second and third member of the barrel locking mechanism 640 a and 640 b.
  • Member 630 acts in combination with members 640 a and 640 b to lock mold 600 after placement of balloon catheter 210 and stent 220 into grooves 610 a or 610 b and closing mold 600 .
  • the barrel locking mechanism inhibits or prevents mold 600 from opening when balloon catheter 210 is expanding.
  • halves 610 a and 610 b need not be coupled together via hinge 615 .
  • FIG. 7 is a diagram illustrating a cross section of mold 600 .
  • Closing mold 600 forms bore 625 in which a mounted stent 220 is disposed.
  • Mounted stent 220 is aligned with half washers 650 such that the distal end of the stent 220 is in alignment with a first pair of half washers 650 and the proximal end is in alignment with a second pair of half washers 650 .
  • Half washers 650 on the same mold half are spaced apart at a length equal to about the length of mounted stent 220 .
  • Half washers can extend several thousandths of an inch into the bore of the mold 600 (e.g., about 0.002 to about 0.005 inches, or more narrowly about 0.003 to about 0.004).
  • Half washers can have a width of about 0.5 mm to about 4 mm or slightly less than half the length of the stent.
  • mold 600 includes only a single pair of half washers 650 that are positioned at one end of stent 220 , preferably the leading edge of stent 220 (i.e., the edge of stent 220 that faces the direction of travel during installation of stent 220 ). Accordingly, stent 220 would have a single tapered end that would facilitate deliverability of stent 220 .
  • balloon catheter 210 is heated and expanded. Specifically, balloon catheter 210 is heated up to about 190° F. to soften balloon catheter 210 , thereby causing expansion (referred to as thermogripping). Internal pressure is supplied to the balloon catheter 210 to cause further expansion. Specifically, about 120 PSI to about 330 PSI, or more narrowly about 150 PSI to about 290 PSI, can be applied to cause expansion of catheter 210 .
  • Expansion of balloon catheter 210 causes balloon catheter 210 to press against the inner diameter of stent 220 .
  • Expansion of balloon catheter 210 causes a majority of stent 220 to expand to the diameter of bore 625 of mold 600 .
  • Half washers 650 prevent ends of stent 220 aligned with the half washers 650 from expanding to the diameter of bore 625 of mold 600 . As the ends of the stent 220 press against the half washers 650 , the ends of the stent 220 are prevented from expanding, thereby yielding a stent profile with inward tapered ends.
  • a mold bore may have a proximal section tapering inward to a proximal end of the mold bore and a distal section tapering inward to a distal end of the mold bore.
  • the tapered sections may be adapted to mold tapered sections of the stent that improve the attachment of the stent to the delivery system and that facilitate the delivery of the mounted stent into and through a bodily lumen.
  • the mold bore may taper inward relatively uniformly between a proximal section and a distal section.
  • FIG. 8 is a diagram illustrating a mold 800 according to another embodiment of the invention.
  • Mold 800 is substantially similar to mold 600 except that mold 800 includes a mold block 850 rather than washers 650 .
  • mold 800 includes two mold halves 810 a and 810 b coupled together via a hinge 815 .
  • Half 810 a includes a groove 820 a having a mold block 850 and half 810 b includes a groove 820 b having a mold block 850 .
  • a barrel lock mechanism 830 is coupled to half 810 a.
  • Mechanism 830 acts in combination with barrel lock mechanisms 840 a and 840 b that are coupled to half 810 b, to lock mold 800 shut after placement of a stent 520 within.
  • FIG. 9 is a diagram illustrating an axial cross section of a mold 800 that may mold stent 300 depicted in FIG. 3 .
  • Mold block 850 (and a resulting stent 300 shown in FIG. 3 after balloon catheter 220 expands) has an arrow-like shape in which a mold bore 855 of mold block 850 tapers inward relatively uniformly from a proximal to a distal end of bore 855 .
  • the diameter of mold bore 855 of mold block 850 gradually increases from a distal end to a proximal end.
  • the distal end or leading end may have a diameter of about 0.038 inches.
  • the diameter may increase to a point proximate to the proximal end to a diameter of about 0.041 inches (e.g., at about 5.5 mm from the leading end in a 6 mm stent).
  • the diameter may taper off from about 0.041 inches to about 0.038 inches (from about 0.5 mm from the proximal end in a 6 mm stent).
  • the mold bore may taper inward relatively uniformly from an intermediate point between a proximal end and a distal end to the proximal end.
  • the mold bore may also taper inward relatively uniformly from the intermediate point to the distal end.
  • FIG. 10 is a diagram illustrating a cross section of a mold 1000 according another embodiment of the invention for molding stent 410 in FIG. 4 .
  • the mold 1000 is substantially similar to the mold 600 except that mold block 650 is replaced with a mold block 1050 .
  • Bore 1055 of mold block 1050 tapers inward from approximately a midpoint along bore 1055 toward both a distal and proximal end of bore 1055 .
  • the slope of the taper is such that expansion of a stent 420 in mold 1000 yields a stent 420 having a smaller diameter at the proximal and distal ends with a gradually increasing diameter to a maximum diameter at the middle of stent 420 .
  • a mold bore of a mold member may have a section with a cross-section that oscillates in size between a proximal section and a distal section.
  • the oscillating cross section may be configured to mold a stent mounted on a delivery system to have an oscillating cross section.
  • the oscillating cross section of the stent may improve flexibility of the mounted stent during delivery.
  • FIG. 11 is a diagram illustrating a cross section of a mold 1100 according another embodiment of the invention for molding stent 520 in FIG. 5 .
  • Mold 1100 is substantially similar to the mold 600 except that a mold block 1150 replaces mold block 650 .
  • Mold block 1150 is approximately the length of stent 520 .
  • Bore 1155 of mold block 1150 has a diameter than varies along its length with larger diameter sections alternating with smaller diameter sections.
  • the inner surfaces of mold block 1150 have a wave-like profile.
  • the mold block 1150 can take the form of a sine wave.
  • bore 1155 of mold block 1150 can have three crests and four troughs, with troughs occurring at the proximal and distal ends.
  • mold block 1150 matches the length of the stent (e.g., about 6 mm) and features three crests and four troughs, wherein two troughs are aligned with the proximal and distal ends of the stent 520 .
  • Expansion of balloon catheter 210 causes stent 520 to take the shape of bore 1155 of mold block 1150 , e.g., the stent 520 develops a wave profile, which secures stent 520 to balloon catheter 210 while maintaining flexibility and facilitating deliverability.
  • the height variation between crests and troughs is a few thousands of an inch, e.g., about 0.001 to about 0.005 inches, or more narrowly, about 0.003 to about 0.004.
  • FIG. 12 is a flowchart illustrating a method 1200 of gripping a stent on a catheter according to an embodiment of the invention.
  • a stent is mounted ( 1210 ) on a catheter, as is known to those of ordinary skill in the art.
  • the mounted stent in then placed ( 1220 ) in a groove of a mold (e.g., the molds 600 , 800 , 1000 or 1100 ) and aligned with the washers or blocks.
  • the mold is then closed ( 1230 ) and locked.
  • Heat is then applied ( 1240 ) to the balloon catheter 210 to cause the balloon catheter 210 to soften and therefore more easily expand.
  • the heat can reach up to about 190° F.
  • the balloon catheter 210 is then expanded ( 1250 ) by applying internal air pressure, e.g., about 120 PSI to about 330 PSI, or more narrowly about 150 PSI to about 290 PSI.
  • internal air pressure e.g., about 120 PSI to about 330 PSI, or more narrowly about 150 PSI to about 290 PSI.
  • the balloon catheter 210 expands and presses into the stent, causing the stent to expand until the stent matches the diameter of the bore of the mold.
  • the stent then takes on the shape of the mold.
  • the mounted stent is then removed ( 1260 ) from the mold after the mold is unlocked.
  • heat may facilitate expansion of the stent.
  • Heat may be applied to the device and/or the delivery system prior to and/or during expanding the device. Heat may be applied by pumping heated fluid into a delivery system, such as balloon catheter. Alternatively heat applied by blowing a heated inert gas (e.g., air, nitrogen, oxygen, argon, etc.) onto the device and/or the delivery system.
  • a heated inert gas e.g., air, nitrogen, oxygen, argon, etc.

Abstract

Embodiments of stents having profiles that improve gripping of the stent on a stent delivery system are provided. Additionally, embodiments of molds for fabricating the stents are provided. A radially expandable stent can comprise a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent. The tapered sections can be adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a divisional of application Ser. No. 12/101,044, filed Apr. 10, 2008, now U.S. Pat. No. 7,708,548, which is a divisional of Ser. No. 11/105,004, filed Apr. 12, 2005, now U.S. Pat. No. 7,381,048, both of which are incorporated herein by reference.
  • TECHNICAL FIELD
  • This invention relates generally to stent delivery apparatuses, and more particularly, but not exclusively, to a stent for gripping a balloon catheter and a mold for fabricating the stent.
  • BACKGROUND
  • Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent. Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of affected vessels. Typically stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at a desired location. Examples in the patent literature disclosing stents include U.S. Pat. No. 4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to Gianturco, and U.S. Pat. No. 4,886,062 issued to Wiktor.
  • Conventionally, stents are delivered to the desired location by crimping the stent tightly onto a balloon catheter and transporting the crimped stent/balloon catheter combination to the desired location through a patient's vasculature. Alternatively or in addition to the crimping, the balloon catheter is expanded to contact the inner diameter of the stent. At the desired location, the balloon catheter is expanded, thereby expanding the stent to contact the inner diameter of the patient's artery. The balloon catheter is then deflated and removed from the vasculature.
  • Since the stent and catheter travel through the patient's vasculature, the stent must have a small diameter so that it can pass through small lumens of the patient's vasculature. Secure attachment to the catheter is desirable so that the stent does not prematurely detach from the catheter. The stent should also be sufficiently flexibility to travel through curvatures in the patient's vasculature.
  • However, conventional crimping techniques can be uneven, leading to sharp edges on the crimped stent that can damage or get caught on the patient's vasculature during delivery. Further, crimping can decrease flexibility of the stent, making it hard to deliver the stent through curvatures in the patient's vasculature.
  • If the balloon catheter is expanded before delivery, the balloon catheter may cause excessive expansion of the stent, thereby making it hard to transport the stent through the patient's vasculature (e.g., cross tight lesions). Further, expansion of the balloon catheter can cause the distal and proximal ends of the stent to expand further than the rest of the stent, causing the distal and proximal ends to have upward tapered edges that can get caught in the patient's vasculature, thereby decreasing deliverability.
  • Accordingly, improved methods and devices are desirable for gripping a stent to a balloon catheter that reduce or eliminated the deficiencies mentioned above.
  • SUMMARY
  • Briefly and in general terms, the present invention is directed to a stent and mold for a stent. In aspects of the present invention, a stent comprises a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent, the tapered sections being adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.
  • In other aspects of the present invention, a mold comprises a mold member having a projection into a proximal section of a mold bore of the mold member, the projection configured to mold a tapered section at a proximal end of a stent mounted on a delivery system, the tapered section adapted to improve the attachment of the stent to the delivery system and facilitate the delivery of the mounted stent into and through a bodily lumen.
  • In other aspects of the present invention, a mold comprises a mold member comprising a mold bore configured to mold a stent mounted on a delivery system. The mold bore has a proximal section tapering inward to a proximal end of the mold bore and a distal section tapering inward to a distal end of the mold bore. The tapered sections are adapted to mold tapered sections of the stent that improve the attachment of the stent to the delivery system and that facilitate the delivery of the mounted stent into and through a bodily lumen.
  • The features and advantages of the invention will be more readily understood from the following detailed description which should be read in conjunction with the accompanying drawings.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • Non-limiting and non-exhaustive embodiments of the present invention are described with reference to the following figures, wherein like reference numerals refer to like parts throughout the various views unless otherwise specified.
  • FIG. 1 is an illustration of a stent.
  • FIG. 2 is a diagram illustrating a stent installed on a balloon catheter using the mold of FIG. 7.
  • FIG. 3 is a diagram illustrating a stent formed using the mold of FIG. 9.
  • FIG. 4 is a diagram illustrating a stent formed using the mold of FIG. 10.
  • FIG. 5 is a diagram illustrating a stent formed using the mold of FIG. 11.
  • FIG. 6 is a diagram illustrating a mold according to an embodiment of the invention.
  • FIG. 7 is a diagram illustrating a cross section of the mold of FIG. 6.
  • FIG. 8 is a diagram illustrating a mold according to another embodiment of the invention.
  • FIG. 9 is a diagram illustrating a cross section of the mold of FIG. 8.
  • FIG. 10 is a diagram illustrating a cross section of a mold according another embodiment of the invention.
  • FIG. 11 is a diagram illustrating a cross section of a mold according another embodiment of the invention.
  • FIG. 12 is a flowchart illustrating a method of gripping a stent on a catheter according to an embodiment of the invention.
  • DETAILED DESCRIPTION
  • The following description is provided to enable any person having ordinary skill in the art to make and use the invention, and is provided in the context of a particular application and its requirements. Various modifications to the embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown, but is to be accorded the widest scope consistent with the principles, features and teachings disclosed herein.
  • The term “implantable medical device” is intended to include self-expandable stents, balloon-expandable stents, stent-grafts, and grafts. The structural pattern of the device can be of virtually any design. A stent, for example, may include a pattern or network of interconnecting structural elements or struts. FIG. 1 depicts an example of a three-dimensional view of a stent 10. The stent may have a pattern that includes a number of interconnecting elements or struts 15. The embodiments disclosed herein are not limited to stents or to the stent pattern illustrated in FIG. 1. The embodiments are easily applicable to other patterns and other devices. The variations in the structure of patterns are virtually unlimited. As shown in FIG. 1 the geometry or shape of a stent varies throughout its structure.
  • In some embodiments, a stent may be formed from a tube by laser cutting the pattern of struts in the tube. The stent may also be formed by laser cutting a polymeric or metallic sheet, rolling the pattern into the shape of the cylindrical stent, and providing a longitudinal weld to form the stent. Other methods of forming stents are well known and include chemically etching a sheet and rolling and then welding it to form the stent. A polymeric or metallic wire may also be coiled to form the stent. The stent may be formed by injection molding of a thermoplastic or reaction injection molding of a thermoset polymeric material. Filaments of the compounded polymer may be extruded or melt spun. These filaments can then be cut, formed into ring elements, welded closed, corrugated to form crowns, and then the crowns welded together by heat or solvent to form the stent. Lastly, hoops or rings may be cut from tubing stock, the tube elements stamped to form crowns, and the crowns connected by welding or laser fusion to form the stent.
  • Additionally, an implantable medical device may be configured to degrade after implantation by fabricating the device either partially or completely from biodegradable polymers. Polymers can be biostable, bioabsorbable, biodegradable, or bioerodable. Biostable refers to polymers that are not biodegradable. The terms biodegradable, bioabsorbable, and bioerodable, as well as degraded, eroded, and absorbed, are used interchangeably and refer to polymers that are capable of being completely eroded or absorbed when exposed to bodily fluids such as blood and can be gradually resorbed, absorbed, and/or eliminated by the body.
  • Furthermore, a biodegradable device may be intended to remain in the body for a duration of time until its intended function of, for example, maintaining vascular patency and/or drug delivery is accomplished. For biodegradable polymers used in coating applications, after the process of degradation, erosion, absorption, and/or resorption has been completed, no polymer will remain on the stent. In some embodiments, very negligible traces or residue may be left behind. The duration is typically in the range of six to twelve months.
  • Representative examples of polymers that may be used to fabricate embodiments of implantable medical devices disclosed herein include, but are not limited to, poly(N-acetylglucosamine)(Chitin), Chitosan, poly(3-hydroxyvalerate), poly(lactide-co-glycolide), poly(3-hydroxybutyrate), poly(4-hydroxybutyrate), poly(3-hydroxybutyrate-co-3-hydroxyvalerate), polyorthoester, polyanhydride, poly(glycolic acid), poly(glycolide), poly(L-lactic acid), poly(L-lactide), poly(D,L-lactic acid), poly(D,L-lactide), poly(L-lactide-co-D,L-lactide), poly(caprolactone), poly(L-lactide-co-caprolactone), poly(D,L-lactide-co-caprolactone), poly(glycolide-co-caprolactone), poly(trimethylene carbonate), polyester amide, poly(glycolic acid-co-trimethylene carbonate), co-poly(ether-esters) (e.g. PEO/PLA), polyphosphazenes, biomolecules (such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid), polyurethanes, silicones, polyesters, polyolefins, polyisobutylene and ethylene-alphaolefin copolymers, acrylic polymers and copolymers other than polyacrylates, vinyl halide polymers and copolymers (such as polyvinyl chloride), polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidene halides (such as polyvinylidene chloride), polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters (such as polyvinyl acetate), acrylonitrile-styrene copolymers, ABS resins, polyamides (such as Nylon 66 and polycaprolactam), polycarbonates, polyoxymethylenes, polyimides, polyethers, polyurethanes, rayon, rayon-triacetate, cellulose, cellulose acetate, cellulose butyrate, cellulose acetate butyrate, cellophane, cellulose nitrate, cellulose propionate, cellulose ethers, and carboxymethyl cellulose. Additional representative examples of polymers that may be especially well suited for use in fabricating embodiments of implantable medical devices disclosed herein include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL), poly(butyl methacrylate), poly(vinylidene fluoride-co-hexafluoropropene) (e.g., SOLEF 21508, available from Solvay Solexis PVDF, Thorofare, N.J.), polyvinylidene fluoride (otherwise known as KYNAR, available from ATOFINA Chemicals, Philadelphia, Pa.), ethylene-vinyl acetate copolymers, poly(vinyl acetate), styrene-isobutylene-styrene triblock copolymers, and polyethylene glycol.
  • In addition, a device may be made of a metallic material or an alloy such as, but not limited to, cobalt chromium alloy (ELGILOY), stainless steel (316L), high nitrogen stainless steel, e.g., BIODUR 108, cobalt chrome alloy L-605, “MP35N,” “MP20N,” ELASTINITE (Nitinol), tantalum, nickel-titanium alloy, platinum-iridium alloy, gold, magnesium, or combinations thereof “MP35N” and “MP20N” are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co., Jenkintown, Pa. “MP35N” consists of 35% cobalt, 35% nickel, 20% chromium, and 10% molybdenum. “MP20N” consists of 50% cobalt, 20% nickel, 20% chromium, and 10% molybdenum.
  • As discussed above, delivery of a stent is facilitated by a secure attachment of the stent to a delivery system and by flexibility of the stent. A small profile stent (crimped tightly) with a small stent diameter allows for secure attachment and eases transport through narrow lumen passages. However, decreasing a profile of a stent also decreases flexibility of the stent. Conversely, a larger profile stent (expanded stent) with a large stent diameter allows for greater flexibility. However, a large profile makes transport through narrow lumen passages more difficult.
  • The negative effects on delivery of a small and large profile can be reconciled by using a stent having both large and small profile sections. The small profile sections facilitate secure attachment, while the large profile sections facilitate flexibility. Furthermore, a small profile section at or proximate to a stent end that is a leading end or edge during delivery may be particularly helpful in facilitating delivery. Various embodiments of implantable medical devices, such as stents, having at least these characteristic are disclosed herein.
  • Certain embodiments of an implantable medical device, such as a radially expandable stent, mounted on a delivery system may include a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent. The tapered sections may be adapted to improve the attachment of the stent to the delivery system. Additionally, the tapered section may facilitate the delivery of the mounted device into and through a bodily lumen.
  • Facilitating delivery may include facilitating smooth communication of device through a lumen without substantially limiting the ability of device to bend around curvatures in the lumen. Facilitating delivery also may include improving a grip or attachment of the device on the delivery system since. A tapered portion of a device may tend to strengthen a grip of the device on the delivery system. Thus a tapered section may inhibit or prevent disengagement of the device from the delivery system.
  • In one embodiment, at least a portion of the stent may have a cross-section that is circular or substantially circular. A delivery system may be, for example, a balloon catheter for delivering a stent.
  • As an illustration, FIG. 2 depicts an axial cross section of a stent 220 having tapered sections 230 and 240 at a distal end and a proximal end, respectively. Stent 220 may be installed on balloon catheter 210 using a mold 600 in FIG. 7. Installed stent 220 has a profile in which proximal section 230 and distal section 240 of stent 220 exhibit an inward taper, instead of straight or outward taper outwards, as with conventional stents.
  • Accordingly, stent 220 can more easily travel through a patient's vasculature during delivery and is less likely to get caught in or damage the vasculature. Further, since the majority of stent 220 has an expanded profile, stent 220 can still track curvatures in the vasculature.
  • Additionally, the profile also causes stent 220 to “hug” or grip balloon catheter 210, thereby increasing the ability of stent 220 to stay mounted to the balloon catheter during delivery (until balloon 210 is deflated).
  • In some embodiments, an implantable medical device, such as a stent, mounted on a delivery system may have a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent. The tapered sections may be adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.
  • In one embodiment, a device may have profile that tapers inward relatively uniformly between the proximal section and the distal section. Thus, the mounted stent may have an “arrow-like” shape. As an illustration, FIG. 3 depicts a stent 300 having a proximal section 310 that is tapered inward toward a proximal end. Stent 300 also has a section 320 that tapers inward relatively uniformly from the proximal section to a distal end to adopt an arrow-like shape. Stent 300 may be installed on a balloon catheter using a mold 800 in FIG. 9.
  • As indicated above, a small profile at a leading end or edge of a stent is particularly advantageous. To facilitate delivery, the distal end may be a leading edge during delivery. A “leading edge” is the edge of stent that faces the direction of travel during implantation of the stent.
  • In another embodiment, the proximal section may taper inward relatively uniformly from an intermediate point between the proximal end and the distal end to the proximal end. The distal section may taper inward relatively uniformly from the intermediate point to the distal end.
  • As an illustration, FIG. 4 depicts a stent 410 having a proximal section 420 and a distal section 430 that taper inward relatively uniformly from an intermediate point 440. Stent 410 has a diameter that gradually increases from a minimum value at the proximal and distal ends to a maximum value at intermediate point 440. Intermediate point 440, for example, may be approximately midway between the proximal and distal ends of the stent. Stent 410 may be installed on a balloon catheter using a mold 1000 in FIG. 10.
  • In one embodiment, a diameter of a stent that is about 6 mm long and about 0.041 inches in diameter at its midpoint can have a diameter at the distal and proximal ends between about 0.037 inches to about 0.038 inches.
  • The profile of stents 220, 300, and 410 facilitate a firm attachment of the stents to a balloon catheter, while maintaining flexibility. Further, the stents may travel more easily through tight lumens due to the small diameter at the ends as compared to conventional stents. Further, the stents are less likely to get caught or damage the patient's vasculature because the stents lack upwardly tapered ends as conventional stents may have after balloon catheter expansion.
  • In further embodiments, an implantable medical device, such as a stent mounted on a delivery system may include a section having a cross-section that oscillates in size between a proximal section and a distal section. The oscillating cross section may be adapted to improve flexibility during delivery of the mounted stent. Such a stent may have a “wave-like” profile with peaks and troughs.
  • The section of a stent having a wave-like profile may have at least one narrow region alternating with at least one wide region. At least a portion of the at least one narrow region is in contact with a surface of the delivery system. In addition, at least a portion of the at least one wide region may not be in contact with the surface of the delivery system. Thus, narrow regions may allow the stent to grip a balloon catheter. In addition, the wide regions allow the stent to flex and bend as the mounted stent passes through curved and/or narrow vasculature.
  • FIG. 5 depicts a stent 520 with an oscillating cross section formed using mold 1100 in FIG. 11. Stent 520 has a wave-like shape or profile, which provides the advantages mentioned above. It will be appreciated by one of ordinary skill in the art that stent 520 can take other wave profiles. For example, the profile can include additional crests and troughs and/or can be symmetrical or asymmetrical.
  • Various embodiments of a mold for implantable medical devices that are described herein may include a mold member having a mold bore configured to mold a stent mounted on a delivery system. The mold member may mold the stent after the delivery system expands an outer surface of the stent onto at least a portion of an inner surface that defines the mold bore.
  • A mold member may be composed of more than one piece. In some embodiments, the mold member may be composed of two halves. Each half may have a device-holding groove. The grooves may be configured to form the mold bore when the two halves are joined. In one embodiment, the mold may include a lock adapted to inhibit or prevent opening of the mold during molding of the device.
  • In one embodiment, a mold member may have a projection into a proximal section of a mold bore of the mold member. The projection may be configured to mold a tapered section at a proximal end of an implantable medical device, such as a stent, mounted on a delivery system. The tapered section, as described above, may be adapted to improve the attachment of the stent to the delivery system and facilitate the delivery of the mounted stent into and through a bodily lumen.
  • In another embodiment, the mold member may have a second projection into a distal section of a mold bore of the mold member for molding a tapered section into a distal end of a stent. In some embodiments, the projection may include a cylindrical member having an annulus disposed within the mold.
  • As an illustration, FIG. 6 is a diagram illustrating a mold member or mold 600 according to an embodiment of the invention that may, for example, mold stent 220 in FIG. 2. Mold 600 takes a split mold shape and has two halves: 610 a and 610 b, each having a groove 620 a and 620 b, respectively, running down a longitudinal axis of halves 610 a and 610 b. Halves 610 a and 610 b are coupled together via a hinge 615 that enables mold 600 to open and close via rotation of one half with respect to the other half. Hinge 615 ensures proper alignment of the halves 610 a and 610 b when mold 600 is closed. Grooves 620 a and 620 b are configured to receive and hold a balloon catheter 210 (FIG. 2) and a stent 220 (FIG. 2) in place.
  • Grooves 620 a and 620 b form a mold bore 625 (FIG. 7) through mold 600 when mold 600 is closed, that has a diameter greater than the diameter of stent 220 (e.g., from about 0.003 inches greater to about 0.048 inches greater for a stent which is approximately 0.045 inch in diameter). Grooves 620 a and 620 b each include two half washers 650 spaced apart to approximately match the length of stent 220. Half washers 650 project or extend into grooves 620 a and 620 b.
  • When balloon catheter 210 is expanded (via internal air pressure), balloon catheter 210 pushes against an inner surface of stent 220, causing stent 220 to expand to match the diameter of bore 625 formed by grooves 620 a and 620 b. However, since half washers 650 extend into grooves 620 a and 620 b, the proximal and distal ends of stent 220 cannot expand to the same diameter as the rest of the stent 220 (e.g., to the diameter of bore 625).
  • Accordingly, stent 220 has a profile after molding in which at least a portion of its proximal and distal ends are tapered inwards. The tapered inward edges facilitate smooth communication of stent 220 through a patient's vasculature without substantially limiting the ability of stent 220 to bend around curvatures in the vasculature. Further, the tapered ends tend to grip the balloon catheter 210 better than untapered ends, inhibiting or preventing stent 220 from disengaging from balloon catheter 210 before it is deflated.
  • Half 610 a includes a first member 630 of a barrel locking mechanism. Half 610 b includes a second and third member of the barrel locking mechanism 640 a and 640 b. Member 630 acts in combination with members 640 a and 640 b to lock mold 600 after placement of balloon catheter 210 and stent 220 into grooves 610 a or 610 b and closing mold 600. The barrel locking mechanism inhibits or prevents mold 600 from opening when balloon catheter 210 is expanding.
  • In alternative embodiments of the invention, different locking mechanisms can be used. Further, halves 610 a and 610 b need not be coupled together via hinge 615.
  • FIG. 7 is a diagram illustrating a cross section of mold 600. Closing mold 600 forms bore 625 in which a mounted stent 220 is disposed. Mounted stent 220 is aligned with half washers 650 such that the distal end of the stent 220 is in alignment with a first pair of half washers 650 and the proximal end is in alignment with a second pair of half washers 650. Half washers 650 on the same mold half are spaced apart at a length equal to about the length of mounted stent 220. Half washers can extend several thousandths of an inch into the bore of the mold 600 (e.g., about 0.002 to about 0.005 inches, or more narrowly about 0.003 to about 0.004). Half washers can have a width of about 0.5 mm to about 4 mm or slightly less than half the length of the stent.
  • In an embodiment of the invention, mold 600 includes only a single pair of half washers 650 that are positioned at one end of stent 220, preferably the leading edge of stent 220 (i.e., the edge of stent 220 that faces the direction of travel during installation of stent 220). Accordingly, stent 220 would have a single tapered end that would facilitate deliverability of stent 220.
  • Once stent 220 is disposed within bore 625 of closed mold 600, balloon catheter 210 is heated and expanded. Specifically, balloon catheter 210 is heated up to about 190° F. to soften balloon catheter 210, thereby causing expansion (referred to as thermogripping). Internal pressure is supplied to the balloon catheter 210 to cause further expansion. Specifically, about 120 PSI to about 330 PSI, or more narrowly about 150 PSI to about 290 PSI, can be applied to cause expansion of catheter 210.
  • Expansion of balloon catheter 210 causes balloon catheter 210 to press against the inner diameter of stent 220. Expansion of balloon catheter 210 causes a majority of stent 220 to expand to the diameter of bore 625 of mold 600. Half washers 650 prevent ends of stent 220 aligned with the half washers 650 from expanding to the diameter of bore 625 of mold 600. As the ends of the stent 220 press against the half washers 650, the ends of the stent 220 are prevented from expanding, thereby yielding a stent profile with inward tapered ends.
  • In one embodiment, a mold bore may have a proximal section tapering inward to a proximal end of the mold bore and a distal section tapering inward to a distal end of the mold bore. The tapered sections may be adapted to mold tapered sections of the stent that improve the attachment of the stent to the delivery system and that facilitate the delivery of the mounted stent into and through a bodily lumen. In an embodiment, the mold bore may taper inward relatively uniformly between a proximal section and a distal section.
  • FIG. 8 is a diagram illustrating a mold 800 according to another embodiment of the invention. Mold 800 is substantially similar to mold 600 except that mold 800 includes a mold block 850 rather than washers 650. Specifically, mold 800 includes two mold halves 810 a and 810 b coupled together via a hinge 815. Half 810 a includes a groove 820 a having a mold block 850 and half 810 b includes a groove 820 b having a mold block 850. A barrel lock mechanism 830 is coupled to half 810 a. Mechanism 830 acts in combination with barrel lock mechanisms 840 a and 840 b that are coupled to half 810 b, to lock mold 800 shut after placement of a stent 520 within.
  • FIG. 9 is a diagram illustrating an axial cross section of a mold 800 that may mold stent 300 depicted in FIG. 3. Mold block 850 (and a resulting stent 300 shown in FIG. 3 after balloon catheter 220 expands) has an arrow-like shape in which a mold bore 855 of mold block 850 tapers inward relatively uniformly from a proximal to a distal end of bore 855. The diameter of mold bore 855 of mold block 850 gradually increases from a distal end to a proximal end.
  • Delivery of the stent may be facilitated by having the distal end as the end of the stent that faces the direction of delivery. In one embodiment, the distal end or leading end may have a diameter of about 0.038 inches. The diameter may increase to a point proximate to the proximal end to a diameter of about 0.041 inches (e.g., at about 5.5 mm from the leading end in a 6 mm stent). At the proximal end, the diameter may taper off from about 0.041 inches to about 0.038 inches (from about 0.5 mm from the proximal end in a 6 mm stent).
  • In other embodiments, the mold bore may taper inward relatively uniformly from an intermediate point between a proximal end and a distal end to the proximal end. The mold bore may also taper inward relatively uniformly from the intermediate point to the distal end.
  • FIG. 10 is a diagram illustrating a cross section of a mold 1000 according another embodiment of the invention for molding stent 410 in FIG. 4. The mold 1000 is substantially similar to the mold 600 except that mold block 650 is replaced with a mold block 1050. Bore 1055 of mold block 1050 tapers inward from approximately a midpoint along bore 1055 toward both a distal and proximal end of bore 1055. The slope of the taper is such that expansion of a stent 420 in mold 1000 yields a stent 420 having a smaller diameter at the proximal and distal ends with a gradually increasing diameter to a maximum diameter at the middle of stent 420.
  • In a further embodiment, a mold bore of a mold member may have a section with a cross-section that oscillates in size between a proximal section and a distal section. The oscillating cross section may be configured to mold a stent mounted on a delivery system to have an oscillating cross section. The oscillating cross section of the stent may improve flexibility of the mounted stent during delivery.
  • FIG. 11 is a diagram illustrating a cross section of a mold 1100 according another embodiment of the invention for molding stent 520 in FIG. 5. Mold 1100 is substantially similar to the mold 600 except that a mold block 1150 replaces mold block 650. Mold block 1150 is approximately the length of stent 520. Bore 1155 of mold block 1150 has a diameter than varies along its length with larger diameter sections alternating with smaller diameter sections. As shown in FIG. 11, the inner surfaces of mold block 1150 have a wave-like profile. For example, in profile, the mold block 1150 can take the form of a sine wave. In an embodiment of the invention, bore 1155 of mold block 1150 can have three crests and four troughs, with troughs occurring at the proximal and distal ends.
  • In FIG. 11, mold block 1150 matches the length of the stent (e.g., about 6 mm) and features three crests and four troughs, wherein two troughs are aligned with the proximal and distal ends of the stent 520. Expansion of balloon catheter 210 causes stent 520 to take the shape of bore 1155 of mold block 1150, e.g., the stent 520 develops a wave profile, which secures stent 520 to balloon catheter 210 while maintaining flexibility and facilitating deliverability. The height variation between crests and troughs is a few thousands of an inch, e.g., about 0.001 to about 0.005 inches, or more narrowly, about 0.003 to about 0.004.
  • FIG. 12 is a flowchart illustrating a method 1200 of gripping a stent on a catheter according to an embodiment of the invention. First, a stent is mounted (1210) on a catheter, as is known to those of ordinary skill in the art. The mounted stent in then placed (1220) in a groove of a mold (e.g., the molds 600, 800, 1000 or 1100) and aligned with the washers or blocks. The mold is then closed (1230) and locked. Heat is then applied (1240) to the balloon catheter 210 to cause the balloon catheter 210 to soften and therefore more easily expand. In an embodiment of the invention, the heat can reach up to about 190° F. The balloon catheter 210 is then expanded (1250) by applying internal air pressure, e.g., about 120 PSI to about 330 PSI, or more narrowly about 150 PSI to about 290 PSI. During expansion, the balloon catheter 210 expands and presses into the stent, causing the stent to expand until the stent matches the diameter of the bore of the mold. The stent then takes on the shape of the mold. The mounted stent is then removed (1260) from the mold after the mold is unlocked.
  • In some embodiments, heat may facilitate expansion of the stent. Heat may be applied to the device and/or the delivery system prior to and/or during expanding the device. Heat may be applied by pumping heated fluid into a delivery system, such as balloon catheter. Alternatively heat applied by blowing a heated inert gas (e.g., air, nitrogen, oxygen, argon, etc.) onto the device and/or the delivery system.
  • While particular embodiments of the present invention have been shown and described, it will be obvious to those skilled in the art that changes and modifications can be made without departing from this invention in its broader aspects. Therefore, the appended claims are to encompass within their scope all such changes and modifications as fall within the true spirit and scope of this invention.

Claims (16)

1. A radially expandable stent mounted on a delivery system, the stent comprising:
a proximal section tapering inward to a proximal end of the stent and a distal section tapering inward to a distal end of the stent, the tapered sections being adapted to improve the attachment of the stent to the delivery system and to facilitate the delivery of the mounted device into and through a bodily lumen.
2. The stent of claim 1, wherein the stent comprises a biostable and/or biodegradable polymer.
3. The stent of claim 1, wherein the stent comprises a profile that tapers inward relatively uniformly between the proximal section and the distal section.
4. The stent of claim 1, wherein the proximal section tapers inward relatively uniformly from an intermediate point between the proximal end and the distal end to the proximal end, and wherein the distal section tapers inward relatively uniformly from the intermediate point to the distal end.
5. The stent of claim 1, wherein the delivery system comprises a balloon catheter.
6. A mold for a radially expandable stent, the mold comprising:
a mold member having a projection into a proximal section of a mold bore of the mold member, the projection configured to mold a tapered section at a proximal end of a stent mounted on a delivery system, the tapered section adapted to improve the attachment of the stent to the delivery system and facilitate the delivery of the mounted stent into and through a bodily lumen.
7. The mold of claim 6, further comprising a second projection into a distal section of a mole bore of the mold member.
8. The mold of claim 6, wherein the projection comprises a cylindrical member having an annulus disposed within the mold.
9. The mold of claim 6, wherein the delivery system comprises a balloon catheter.
10. The mold of claim 6, wherein the mold member comprise two halves, each half having a stent-holding groove, the grooves configured to form the mold bore when the two halves are joined.
11. A mold for a radially expandable stent, the mold comprising:
a mold member comprising a mold bore configured to mold a stent mounted on a delivery system, the mold bore having a proximal section tapering inward to a proximal end of the mold bore and a distal section tapering inward to a distal end of the mold bore, the tapered sections being adapted to mold tapered sections of the stent that improve the attachment of the stent to the delivery system and that facilitate the delivery of the mounted stent into and through a bodily lumen.
12. The mold of claim 11, wherein the delivery system comprises a balloon catheter.
13. The mold of claim 11, wherein the mold member molds the device after the delivery system expands an outer surface of the stent onto at least a portion of an inner surface that defines the mold bore.
14. The mold of claim 11, wherein the mold bore tapers inward relatively uniformly between a proximal section and a distal section.
15. The mold of claim 11, wherein the mold bore tapers inward relatively uniformly from an intermediate point between a proximal end and a distal end to the proximal end, and wherein the mold bore tapers inward relatively uniformly from the intermediate point to the distal end.
16. The mold of claim 11, wherein the mold member comprise two halves, each half having a stent-holding groove, the grooves configured to form the mold bore when the two halves are joined.
US12/772,893 2005-04-12 2010-05-03 Stents with profiles for gripping a balloon catheter and molds for fabricating stents Expired - Fee Related US8393887B2 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US12/772,893 US8393887B2 (en) 2005-04-12 2010-05-03 Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US13/794,128 US20130197620A1 (en) 2005-04-12 2013-03-11 Stents with Profiles for Gripping a Balloon Catheter and Molds for Fabricating Stents

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US11/105,004 US7381048B2 (en) 2005-04-12 2005-04-12 Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US12/101,044 US7708548B2 (en) 2005-04-12 2008-04-10 Molds for fabricating stents with profiles for gripping a balloon catheter
US12/772,893 US8393887B2 (en) 2005-04-12 2010-05-03 Stents with profiles for gripping a balloon catheter and molds for fabricating stents

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US12/101,044 Division US7708548B2 (en) 2005-04-12 2008-04-10 Molds for fabricating stents with profiles for gripping a balloon catheter

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US13/794,128 Division US20130197620A1 (en) 2005-04-12 2013-03-11 Stents with Profiles for Gripping a Balloon Catheter and Molds for Fabricating Stents

Publications (2)

Publication Number Publication Date
US20100217378A1 true US20100217378A1 (en) 2010-08-26
US8393887B2 US8393887B2 (en) 2013-03-12

Family

ID=36950295

Family Applications (4)

Application Number Title Priority Date Filing Date
US11/105,004 Active 2026-08-26 US7381048B2 (en) 2005-04-12 2005-04-12 Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US12/101,044 Expired - Fee Related US7708548B2 (en) 2005-04-12 2008-04-10 Molds for fabricating stents with profiles for gripping a balloon catheter
US12/772,893 Expired - Fee Related US8393887B2 (en) 2005-04-12 2010-05-03 Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US13/794,128 Abandoned US20130197620A1 (en) 2005-04-12 2013-03-11 Stents with Profiles for Gripping a Balloon Catheter and Molds for Fabricating Stents

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US11/105,004 Active 2026-08-26 US7381048B2 (en) 2005-04-12 2005-04-12 Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US12/101,044 Expired - Fee Related US7708548B2 (en) 2005-04-12 2008-04-10 Molds for fabricating stents with profiles for gripping a balloon catheter

Family Applications After (1)

Application Number Title Priority Date Filing Date
US13/794,128 Abandoned US20130197620A1 (en) 2005-04-12 2013-03-11 Stents with Profiles for Gripping a Balloon Catheter and Molds for Fabricating Stents

Country Status (4)

Country Link
US (4) US7381048B2 (en)
EP (1) EP1874230A2 (en)
JP (1) JP2008535627A (en)
WO (1) WO2006110474A2 (en)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20220354631A1 (en) * 2018-11-19 2022-11-10 Pulmair Medical, Inc. Implantable Artificial Bronchus

Families Citing this family (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8240020B2 (en) * 2006-06-30 2012-08-14 Advanced Cardiovascular Systems, Inc. Stent retention mold and method
US7740791B2 (en) * 2006-06-30 2010-06-22 Advanced Cardiovascular Systems, Inc. Method of fabricating a stent with features by blow molding
KR100826664B1 (en) * 2006-11-01 2008-05-02 주식회사 엠아이텍 Stent and method of manufacturing the same
EP2349129B1 (en) * 2008-10-10 2016-05-04 Veryan Medical Limited A stent suitable for deployment in a blood vessel
US9149377B2 (en) 2008-10-10 2015-10-06 Veryan Medical Ltd. Stent suitable for deployment in a blood vessel
US20100244305A1 (en) * 2009-03-24 2010-09-30 Contiliano Joseph H Method of manufacturing a polymeric stent having improved toughness
US8524132B2 (en) 2010-04-14 2013-09-03 Abbott Cardiovascular Systems Inc. Method of fabricating an intraluminal scaffold with an enlarged portion
WO2012074546A2 (en) * 2010-11-16 2012-06-07 Aldila Golf Corporation High straightness arrow and method of manufacture
US10161727B2 (en) 2010-11-16 2018-12-25 Aldila Golf Corporation High straightness arrow and method of manufacture
US9448045B2 (en) 2010-11-16 2016-09-20 Aldila Golf Corp. High straightness arrow and method of manufacture
CN102371670A (en) * 2011-10-14 2012-03-14 微创医疗器械(上海)有限公司 New processing method of biodegradable stent
KR101330397B1 (en) * 2011-11-01 2013-11-15 재단법인 아산사회복지재단 A device for blood vessel anastomosis using the self-expandable material or structure and a method for blood vessel anastomosis using the same
US9433991B2 (en) 2011-12-21 2016-09-06 Edwards Lifesciences Corporation Apparatus and method for stent shaping
WO2013115141A1 (en) * 2012-01-30 2013-08-08 川澄化学工業株式会社 Biliary stent
EP2991581B1 (en) * 2013-05-03 2018-06-06 Amaranth Medical PTE Stent delivery apparatus
US10064745B2 (en) * 2014-03-18 2018-09-04 Abbott Cardiovascular Systems Inc. Tapered scaffolds
CN104644295B (en) * 2014-12-19 2019-07-16 上海百心安生物技术有限公司 A kind of absorbable intraluminal stent and preparation method thereof
CN106880428B (en) * 2017-03-28 2019-08-09 上海百心安生物技术有限公司 A kind of bioabsorbable stent system and method
CN108407266A (en) * 2018-03-16 2018-08-17 黎悦 Microtubular shaping device
CN113827386B (en) * 2021-11-29 2022-03-29 艾柯医疗器械(北京)有限公司 Self-expanding type stent leading-in device

Citations (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4130617A (en) * 1977-12-30 1978-12-19 Airco, Inc. Method of making endotracheal tube cuffs
US4264294A (en) * 1979-01-08 1981-04-28 Ruiz Oscar F Profiling die
US5630830A (en) * 1996-04-10 1997-05-20 Medtronic, Inc. Device and method for mounting stents on delivery systems
US5653691A (en) * 1996-04-25 1997-08-05 Rupp; Garry Eugene Thickened inner lumen for uniform stent expansion and method of making
US5672169A (en) * 1996-04-10 1997-09-30 Medtronic, Inc. Stent mounting device
US6290485B1 (en) * 1995-03-02 2001-09-18 Lixiao Wang Mold for forming a balloon catheter having stepped compliance curve
US6387117B1 (en) * 1999-09-22 2002-05-14 Scimed Life Systems, Inc. Stent crimping system
US20020077690A1 (en) * 2000-12-18 2002-06-20 Lixiao Wang Catheter for controlled stent delivery
US20020099406A1 (en) * 1997-05-22 2002-07-25 St. Germain Jon P. Variable expansion force stent
JP2002233579A (en) * 2000-12-04 2002-08-20 Piolax Medical Device:Kk Method of manufacturing for metallic stent
US6464720B2 (en) * 1997-09-24 2002-10-15 Cook Incorporated Radially expandable stent
US6481262B2 (en) * 1999-12-30 2002-11-19 Advanced Cardiovascular Systems, Inc. Stent crimping tool
US6540774B1 (en) * 1999-08-31 2003-04-01 Advanced Cardiovascular Systems, Inc. Stent design with end rings having enhanced strength and radiopacity
US6569193B1 (en) * 1999-07-22 2003-05-27 Advanced Cardiovascular Systems, Inc. Tapered self-expanding stent
US6676697B1 (en) * 1996-09-19 2004-01-13 Medinol Ltd. Stent with variable features to optimize support and method of making such stent
US6726713B2 (en) * 2000-08-09 2004-04-27 Biotronik Mess- Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin Method and device for crimping a stent
US6776604B1 (en) * 2001-12-20 2004-08-17 Trivascular, Inc. Method and apparatus for shape forming endovascular graft material
US20040249435A1 (en) * 2003-06-09 2004-12-09 Xtent, Inc. Stent deployment systems and methods
US6911041B1 (en) * 1997-10-23 2005-06-28 C. R. Bard, Inc. Expanded stent and a method for producing same
US6948223B2 (en) * 2002-05-03 2005-09-27 Medtronic Vascular, Inc. Apparatus for mounting a stent onto a stent delivery system
US7055237B2 (en) * 2003-09-29 2006-06-06 Medtronic Vascular, Inc. Method of forming a drug eluting stent
US7097440B2 (en) * 2000-07-14 2006-08-29 Advanced Cardiovascular Systems, Inc. Embolic protection systems
US20080208254A1 (en) * 2005-07-06 2008-08-28 Steffen Berger Sucking and Chewing Article for Babies or Small Children

Family Cites Families (290)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1237035A (en) 1969-08-20 1971-06-30 Tsi Travmatologii I Ortopedii Magnesium-base alloy for use in bone surgery
US3900632A (en) 1970-02-27 1975-08-19 Kimberly Clark Co Laminate of tissue and random laid continuous filament web
US3839743A (en) 1972-04-21 1974-10-08 A Schwarcz Method for maintaining the normal integrity of blood
US4104410A (en) 1973-12-21 1978-08-01 Malecki George J Processing of green vegetables for color retention in canning
US4110497A (en) 1976-07-02 1978-08-29 Snyder Manufacturing Co., Ltd. Striped laminate and method and apparatus for making same
JPS6037735B2 (en) 1978-10-18 1985-08-28 住友電気工業株式会社 Artificial blood vessel
DE2928007A1 (en) 1979-07-11 1981-01-15 Riess Guido Dr BONE IMPLANT BODY FOR PROSTHESES AND BONE CONNECTORS AND METHOD FOR THE PRODUCTION THEREOF
US4346028A (en) 1979-12-14 1982-08-24 Monsanto Company Asbestiform crystalline calcium sodium or lithium phosphate, preparation and compositions
DE3019996A1 (en) 1980-05-24 1981-12-03 Institute für Textil- und Faserforschung Stuttgart, 7410 Reutlingen HOHLORGAN
US4902289A (en) 1982-04-19 1990-02-20 Massachusetts Institute Of Technology Multilayer bioreplaceable blood vessel prosthesis
US4517687A (en) 1982-09-15 1985-05-21 Meadox Medicals, Inc. Synthetic woven double-velour graft
US4656083A (en) 1983-08-01 1987-04-07 Washington Research Foundation Plasma gas discharge treatment for improving the biocompatibility of biomaterials
US4594407A (en) 1983-09-20 1986-06-10 Allied Corporation Prosthetic devices derived from krebs-cycle dicarboxylic acids and diols
US5197977A (en) 1984-01-30 1993-03-30 Meadox Medicals, Inc. Drug delivery collagen-impregnated synthetic vascular graft
US4633873A (en) 1984-04-26 1987-01-06 American Cyanamid Company Surgical repair mesh
US4596574A (en) 1984-05-14 1986-06-24 The Regents Of The University Of California Biodegradable porous ceramic delivery system for bone morphogenetic protein
CH671337A5 (en) 1984-06-19 1989-08-31 Ceskoslovenska Akademie Ved
US4879135A (en) 1984-07-23 1989-11-07 University Of Medicine And Dentistry Of New Jersey Drug bonded prosthesis and process for producing same
IT1186142B (en) 1984-12-05 1987-11-18 Medinvent Sa TRANSLUMINAL IMPLANTATION DEVICE
US4718907A (en) 1985-06-20 1988-01-12 Atrium Medical Corporation Vascular prosthesis having fluorinated coating with varying F/C ratio
US4818559A (en) 1985-08-08 1989-04-04 Sumitomo Chemical Company, Limited Method for producing endosseous implants
US4733665C2 (en) 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4743252A (en) 1986-01-13 1988-05-10 Corvita Corporation Composite grafts
EP0257091B1 (en) 1986-02-24 1993-07-28 Robert E. Fischell An intravascular stent and percutaneous insertion system
US4878906A (en) 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
EP0241838B1 (en) 1986-04-07 1992-04-15 Agency Of Industrial Science And Technology Antithrombogenic material
US4740207A (en) 1986-09-10 1988-04-26 Kreamer Jeffry W Intralumenal graft
US4723549A (en) 1986-09-18 1988-02-09 Wholey Mark H Method and apparatus for dilating blood vessels
US4722335A (en) 1986-10-20 1988-02-02 Vilasi Joseph A Expandable endotracheal tube
US4800882A (en) 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US4816339A (en) 1987-04-28 1989-03-28 Baxter International Inc. Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation
US5527337A (en) 1987-06-25 1996-06-18 Duke University Bioabsorbable stent and method of making the same
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US4886062A (en) 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US4877030A (en) 1988-02-02 1989-10-31 Andreas Beck Device for the widening of blood vessels
US5192311A (en) 1988-04-25 1993-03-09 Angeion Corporation Medical implant and method of making
US4994298A (en) 1988-06-07 1991-02-19 Biogold Inc. Method of making a biocompatible prosthesis
US5502158A (en) 1988-08-08 1996-03-26 Ecopol, Llc Degradable polymer composition
US5328471A (en) 1990-02-26 1994-07-12 Endoluminal Therapeutics, Inc. Method and apparatus for treatment of focal disease in hollow tubular organs and other tissue lumens
US5019090A (en) 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
CA1322628C (en) 1988-10-04 1993-10-05 Richard A. Schatz Expandable intraluminal graft
US5085629A (en) 1988-10-06 1992-02-04 Medical Engineering Corporation Biodegradable stent
US4977901A (en) 1988-11-23 1990-12-18 Minnesota Mining And Manufacturing Company Article having non-crosslinked crystallized polymer coatings
CH678393A5 (en) 1989-01-26 1991-09-13 Ulrich Prof Dr Med Sigwart
DE69030811T2 (en) 1989-01-27 1997-10-02 Au Membrane & Biotech Res Inst RECEPTOR MEMBRANES AND SELECTIVE CONTROL OF THE ION FLOW BY IONOPHORES
US5163958A (en) 1989-02-02 1992-11-17 Cordis Corporation Carbon coated tubular endoprosthesis
US5289831A (en) 1989-03-09 1994-03-01 Vance Products Incorporated Surface-treated stent, catheter, cannula, and the like
NZ228382A (en) 1989-03-17 1992-08-26 Carter Holt Harvey Plastic Pro Drug administering coil-like device for insertion in body cavity of animal
US5108755A (en) 1989-04-27 1992-04-28 Sri International Biodegradable composites for internal medical use
US5100429A (en) 1989-04-28 1992-03-31 C. R. Bard, Inc. Endovascular stent and delivery system
US4990158A (en) 1989-05-10 1991-02-05 United States Surgical Corporation Synthetic semiabsorbable tubular prosthesis
US5084065A (en) 1989-07-10 1992-01-28 Corvita Corporation Reinforced graft assembly
US5971954A (en) 1990-01-10 1999-10-26 Rochester Medical Corporation Method of making catheter
ATE120377T1 (en) 1990-02-08 1995-04-15 Howmedica INFLATABLE DILATATOR.
US5545208A (en) 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5156623A (en) 1990-04-16 1992-10-20 Olympus Optical Co., Ltd. Sustained release material and method of manufacturing the same
US5123917A (en) 1990-04-27 1992-06-23 Lee Peter Y Expandable intraluminal vascular graft
US5290271A (en) 1990-05-14 1994-03-01 Jernberg Gary R Surgical implant and method for controlled release of chemotherapeutic agents
US5279594A (en) 1990-05-23 1994-01-18 Jackson Richard R Intubation devices with local anesthetic effect for medical use
US6060451A (en) 1990-06-15 2000-05-09 The National Research Council Of Canada Thrombin inhibitors based on the amino acid sequence of hirudin
US5236447A (en) 1990-06-29 1993-08-17 Nissho Corporation Artificial tubular organ
US5342395A (en) 1990-07-06 1994-08-30 American Cyanamid Co. Absorbable surgical repair devices
US5112457A (en) 1990-07-23 1992-05-12 Case Western Reserve University Process for producing hydroxylated plasma-polymerized films and the use of the films for enhancing the compatiblity of biomedical implants
US5455040A (en) 1990-07-26 1995-10-03 Case Western Reserve University Anticoagulant plasma polymer-modified substrate
IL99296A (en) 1990-08-28 1995-12-08 Meadox Medicals Inc Self-supporting woven vascular graft and its preparation
DE69114505T2 (en) 1990-08-28 1996-04-18 Meadox Medicals Inc SELF-SUPPORTING WOVEN VESSEL TRANSPLANT.
US5258020A (en) 1990-09-14 1993-11-02 Michael Froix Method of using expandable polymeric stent with memory
US5163952A (en) 1990-09-14 1992-11-17 Michael Froix Expandable polymeric stent with memory and delivery apparatus and method
US5108417A (en) 1990-09-14 1992-04-28 Interface Biomedical Laboratories Corp. Anti-turbulent, anti-thrombogenic intravascular stent
DE69116130T2 (en) 1990-10-18 1996-05-15 Ho Young Song SELF-EXPANDING, ENDOVASCULAR DILATATOR
US5104410A (en) 1990-10-22 1992-04-14 Intermedics Orthopedics, Inc Surgical implant having multiple layers of sintered porous coating and method
US5163951A (en) 1990-12-27 1992-11-17 Corvita Corporation Mesh composite graft
CS277367B6 (en) 1990-12-29 1993-01-13 Krajicek Milan Three-layered vascular prosthesis
US5178618A (en) * 1991-01-16 1993-01-12 Brigham And Womens Hospital Method and device for recanalization of a body passageway
EP0525210A4 (en) * 1991-02-20 1993-07-28 Tdk Corporation Composite bio-implant and production method therefor
WO1992015342A1 (en) 1991-03-08 1992-09-17 Keiji Igaki Stent for vessel, structure of holding said stent, and device for mounting said stent
US5383925A (en) 1992-09-14 1995-01-24 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5356433A (en) 1991-08-13 1994-10-18 Cordis Corporation Biocompatible metal surfaces
US5811447A (en) 1993-01-28 1998-09-22 Neorx Corporation Therapeutic inhibitor of vascular smooth muscle cells
US6515009B1 (en) * 1991-09-27 2003-02-04 Neorx Corporation Therapeutic inhibitor of vascular smooth muscle cells
US5500013A (en) 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5234457A (en) 1991-10-09 1993-08-10 Boston Scientific Corporation Impregnated stent
US5282860A (en) 1991-10-16 1994-02-01 Olympus Optical Co., Ltd. Stent tube for medical use
US5545408A (en) 1991-10-21 1996-08-13 Peptide Technology Limited Biocompatible implant for the timing of ovulation in mares
US5167614A (en) 1991-10-29 1992-12-01 Medical Engineering Corporation Prostatic stent
US5756476A (en) 1992-01-14 1998-05-26 The United States Of America As Represented By The Department Of Health And Human Services Inhibition of cell proliferation using antisense oligonucleotides
CA2087132A1 (en) 1992-01-31 1993-08-01 Michael S. Williams Stent capable of attachment within a body lumen
US5573934A (en) * 1992-04-20 1996-11-12 Board Of Regents, The University Of Texas System Gels for encapsulation of biological materials
DE69332950T2 (en) 1992-03-31 2004-05-13 Boston Scientific Corp., Natick BLOOD VESSEL FILTER
DE4222380A1 (en) 1992-07-08 1994-01-13 Ernst Peter Prof Dr M Strecker Endoprosthesis implantable percutaneously in a patient's body
US5306294A (en) 1992-08-05 1994-04-26 Ultrasonic Sensing And Monitoring Systems, Inc. Stent construction of rolled configuration
US5514379A (en) 1992-08-07 1996-05-07 The General Hospital Corporation Hydrogel compositions and methods of use
US5853408A (en) 1992-08-20 1998-12-29 Advanced Cardiovascular Systems, Inc. In-vivo modification of the mechanical properties of surgical devices
US5342621A (en) 1992-09-15 1994-08-30 Advanced Cardiovascular Systems, Inc. Antithrombogenic surface
US5830461A (en) 1992-11-25 1998-11-03 University Of Pittsburgh Of The Commonwealth System Of Higher Education Methods for promoting wound healing and treating transplant-associated vasculopathy
US5342348A (en) 1992-12-04 1994-08-30 Kaplan Aaron V Method and device for treating and enlarging body lumens
EP0604022A1 (en) 1992-12-22 1994-06-29 Advanced Cardiovascular Systems, Inc. Multilayered biodegradable stent and method for its manufacture
US5443458A (en) 1992-12-22 1995-08-22 Advanced Cardiovascular Systems, Inc. Multilayered biodegradable stent and method of manufacture
US5981568A (en) 1993-01-28 1999-11-09 Neorx Corporation Therapeutic inhibitor of vascular smooth muscle cells
JP3583801B2 (en) 1993-03-03 2004-11-04 ボストン サイエンティフィック リミテッド Luminal stents and implants
FI92465C (en) * 1993-04-14 1994-11-25 Risto Tapani Lehtinen A method for handling endo-osteal materials
US5441515A (en) 1993-04-23 1995-08-15 Advanced Cardiovascular Systems, Inc. Ratcheting stent
US5464650A (en) 1993-04-26 1995-11-07 Medtronic, Inc. Intravascular stent and method
US5994341A (en) * 1993-07-19 1999-11-30 Angiogenesis Technologies, Inc. Anti-angiogenic Compositions and methods for the treatment of arthritis
EG20321A (en) 1993-07-21 1998-10-31 Otsuka Pharma Co Ltd Medical material and process for producing the same
DE69330132T2 (en) 1993-07-23 2001-11-15 Cook Inc FLEXIBLE STENT WITH A CONFIGURATION MOLDED FROM A MATERIAL SHEET
DK0716610T3 (en) 1993-08-26 2006-09-04 Genetics Inst Llc Human bone morphogenetic proteins for use in neural regeneration
DK0659389T3 (en) 1993-10-20 1999-02-15 Schneider Europ Ag endoprosthesis
US5723004A (en) 1993-10-21 1998-03-03 Corvita Corporation Expandable supportive endoluminal grafts
US5389106A (en) 1993-10-29 1995-02-14 Numed, Inc. Impermeable expandable intravascular stent
US5599301A (en) 1993-11-22 1997-02-04 Advanced Cardiovascular Systems, Inc. Motor control system for an automatic catheter inflation system
SE501288C2 (en) 1993-11-30 1995-01-09 Corimed Gmbh Process for preparing ceramic implant material, preferably hydroxylapatite having ceramic implant material
US5626611A (en) 1994-02-10 1997-05-06 United States Surgical Corporation Composite bioabsorbable materials and surgical articles made therefrom
US5556413A (en) * 1994-03-11 1996-09-17 Advanced Cardiovascular Systems, Inc. Coiled stent with locking ends
US5599922A (en) 1994-03-18 1997-02-04 Lynx Therapeutics, Inc. Oligonucleotide N3'-P5' phosphoramidates: hybridization and nuclease resistance properties
US5726297A (en) * 1994-03-18 1998-03-10 Lynx Therapeutics, Inc. Oligodeoxyribonucleotide N3' P5' phosphoramidates
AU704549B2 (en) 1994-03-18 1999-04-29 Lynx Therapeutics, Inc. Oligonucleotide N3'-P5' phosphoramidates: synthesis and compounds; hybridization and nuclease resistance properties
US5399666A (en) 1994-04-21 1995-03-21 E. I. Du Pont De Nemours And Company Easily degradable star-block copolymers
US5693085A (en) 1994-04-29 1997-12-02 Scimed Life Systems, Inc. Stent with collagen
US5629077A (en) 1994-06-27 1997-05-13 Advanced Cardiovascular Systems, Inc. Biodegradable mesh and film stent
US5670558A (en) 1994-07-07 1997-09-23 Terumo Kabushiki Kaisha Medical instruments that exhibit surface lubricity when wetted
US5554120A (en) 1994-07-25 1996-09-10 Advanced Cardiovascular Systems, Inc. Polymer blends for use in making medical devices including catheters and balloons for dilatation catheters
US5817327A (en) * 1994-07-27 1998-10-06 The Trustees Of The University Of Pennsylvania Incorporation of biologically active molecules into bioactive glasses
US6015429A (en) 1994-09-08 2000-01-18 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US5593403A (en) 1994-09-14 1997-01-14 Scimed Life Systems Inc. Method for modifying a stent in an implanted site
US5578073A (en) 1994-09-16 1996-11-26 Ramot Of Tel Aviv University Thromboresistant surface treatment for biomaterials
US5649977A (en) 1994-09-22 1997-07-22 Advanced Cardiovascular Systems, Inc. Metal reinforced polymer stent
EP0785774B1 (en) * 1994-10-12 2001-01-31 Focal, Inc. Targeted delivery via biodegradable polymers
US5765682A (en) 1994-10-13 1998-06-16 Menlo Care, Inc. Restrictive package for expandable or shape memory medical devices and method of preventing premature change of same
IL115755A0 (en) 1994-10-27 1996-01-19 Medinol Ltd X-ray visible stent
US5836964A (en) 1996-10-30 1998-11-17 Medinol Ltd. Stent fabrication method
US5707385A (en) * 1994-11-16 1998-01-13 Advanced Cardiovascular Systems, Inc. Drug loaded elastic membrane and method for delivery
CA2301351C (en) 1994-11-28 2002-01-22 Advanced Cardiovascular Systems, Inc. Method and apparatus for direct laser cutting of metal stents
US5637113A (en) 1994-12-13 1997-06-10 Advanced Cardiovascular Systems, Inc. Polymer film for wrapping a stent structure
US5919570A (en) 1995-02-01 1999-07-06 Schneider Inc. Slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with a poly(N-vinylpyrrolidone) polymer hydrogel, coated polymer and metal substrate materials, and coated medical devices
US6017577A (en) 1995-02-01 2000-01-25 Schneider (Usa) Inc. Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices
US5876743A (en) * 1995-03-21 1999-03-02 Den-Mat Corporation Biocompatible adhesion in tissue repair
US5605696A (en) 1995-03-30 1997-02-25 Advanced Cardiovascular Systems, Inc. Drug loaded polymeric material and method of manufacture
US6120536A (en) 1995-04-19 2000-09-19 Schneider (Usa) Inc. Medical devices with long term non-thrombogenic coatings
US6099562A (en) 1996-06-13 2000-08-08 Schneider (Usa) Inc. Drug coating with topcoat
US5837313A (en) 1995-04-19 1998-11-17 Schneider (Usa) Inc Drug release stent coating process
JP2795824B2 (en) * 1995-05-12 1998-09-10 オオタ株式会社 Surface treatment method for titanium-based implant and biocompatible titanium-based implant
US5954744A (en) 1995-06-06 1999-09-21 Quanam Medical Corporation Intravascular stent
US5609629A (en) 1995-06-07 1997-03-11 Med Institute, Inc. Coated implantable medical device
US6129761A (en) 1995-06-07 2000-10-10 Reprogenesis, Inc. Injectable hydrogel compositions
US5820917A (en) * 1995-06-07 1998-10-13 Medtronic, Inc. Blood-contacting medical device and method
CA2178541C (en) * 1995-06-07 2009-11-24 Neal E. Fearnot Implantable medical device
US5591199A (en) 1995-06-07 1997-01-07 Porter; Christopher H. Curable fiber composite stent and delivery system
US5667767A (en) 1995-07-27 1997-09-16 Micro Therapeutics, Inc. Compositions for use in embolizing blood vessels
GB9611437D0 (en) 1995-08-03 1996-08-07 Secr Defence Biomaterial
US5830879A (en) 1995-10-02 1998-11-03 St. Elizabeth's Medical Center Of Boston, Inc. Treatment of vascular injury using vascular endothelial growth factor
US5736152A (en) * 1995-10-27 1998-04-07 Atrix Laboratories, Inc. Non-polymeric sustained release delivery system
US5607442A (en) 1995-11-13 1997-03-04 Isostent, Inc. Stent with improved radiopacity and appearance characteristics
US6048964A (en) 1995-12-12 2000-04-11 Stryker Corporation Compositions and therapeutic methods using morphogenic proteins and stimulatory factors
DK2111876T3 (en) * 1995-12-18 2011-12-12 Angiodevice Internat Gmbh Crosslinked polymer preparations and methods for their use
ATE290832T1 (en) 1996-01-05 2005-04-15 Medtronic Inc EXPANDABLE ENDOLUMINAL PROSTHESES
US6150630A (en) 1996-01-11 2000-11-21 The Regents Of The University Of California Laser machining of explosives
EP1011889B1 (en) 1996-01-30 2002-10-30 Medtronic, Inc. Articles for and methods of making stents
JP2000509014A (en) 1996-03-11 2000-07-18 フォーカル,インコーポレイテッド Polymer delivery of radionuclides and radiopharmaceuticals
US6241760B1 (en) 1996-04-26 2001-06-05 G. David Jang Intravascular stent
US6071266A (en) 1996-04-26 2000-06-06 Kelley; Donald W. Lubricious medical devices
US6592617B2 (en) 1996-04-30 2003-07-15 Boston Scientific Scimed, Inc. Three-dimensional braided covered stent
US5733326A (en) * 1996-05-28 1998-03-31 Cordis Corporation Composite material endoprosthesis
US5874165A (en) * 1996-06-03 1999-02-23 Gore Enterprise Holdings, Inc. Materials and method for the immobilization of bioactive species onto polymeric subtrates
US5914182A (en) * 1996-06-03 1999-06-22 Gore Hybrid Technologies, Inc. Materials and methods for the immobilization of bioactive species onto polymeric substrates
US5830178A (en) 1996-10-11 1998-11-03 Micro Therapeutics, Inc. Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide
US5800516A (en) 1996-08-08 1998-09-01 Cordis Corporation Deployable and retrievable shape memory stent/tube and method
US6344271B1 (en) 1998-11-06 2002-02-05 Nanoenergy Corporation Materials and products using nanostructured non-stoichiometric substances
US5855618A (en) * 1996-09-13 1999-01-05 Meadox Medicals, Inc. Polyurethanes grafted with polyethylene oxide chains containing covalently bonded heparin
US6387121B1 (en) 1996-10-21 2002-05-14 Inflow Dynamics Inc. Vascular and endoluminal stents with improved coatings
US5868781A (en) * 1996-10-22 1999-02-09 Scimed Life Systems, Inc. Locking stent
US5833651A (en) 1996-11-08 1998-11-10 Medtronic, Inc. Therapeutic intraluminal stents
US5728751A (en) * 1996-11-25 1998-03-17 Meadox Medicals, Inc. Bonding bio-active materials to substrate surfaces
US5741881A (en) * 1996-11-25 1998-04-21 Meadox Medicals, Inc. Process for preparing covalently bound-heparin containing polyurethane-peo-heparin coating compositions
US5877263A (en) * 1996-11-25 1999-03-02 Meadox Medicals, Inc. Process for preparing polymer coatings grafted with polyethylene oxide chains containing covalently bonded bio-active agents
IT1289728B1 (en) 1996-12-10 1998-10-16 Sorin Biomedica Cardio Spa SYSTEM AND EQUIPMENT DEVICE THAT INCLUDES IT
US5980972A (en) 1996-12-20 1999-11-09 Schneider (Usa) Inc Method of applying drug-release coatings
US6352561B1 (en) * 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US5906759A (en) 1996-12-26 1999-05-25 Medinol Ltd. Stent forming apparatus with stent deforming blades
IT1291001B1 (en) 1997-01-09 1998-12-14 Sorin Biomedica Cardio Spa ANGIOPLASTIC STENT AND ITS PRODUCTION PROCESS
US5733330A (en) 1997-01-13 1998-03-31 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent
US6159951A (en) 1997-02-13 2000-12-12 Ribozyme Pharmaceuticals Inc. 2'-O-amino-containing nucleoside analogs and polynucleotides
US6582472B2 (en) 1997-02-26 2003-06-24 Applied Medical Resources Corporation Kinetic stent
US6210715B1 (en) * 1997-04-01 2001-04-03 Cap Biotechnology, Inc. Calcium phosphate microcarriers and microspheres
US5874101A (en) * 1997-04-14 1999-02-23 Usbiomaterials Corp. Bioactive-gel compositions and methods
US6240616B1 (en) 1997-04-15 2001-06-05 Advanced Cardiovascular Systems, Inc. Method of manufacturing a medicated porous metal prosthesis
US6273913B1 (en) 1997-04-18 2001-08-14 Cordis Corporation Modified stent useful for delivery of drugs along stent strut
FI103715B (en) 1997-04-21 1999-08-31 Vivoxid Oy New composite and its use
US5879697A (en) * 1997-04-30 1999-03-09 Schneider Usa Inc Drug-releasing coatings for medical devices
US5741327A (en) 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US6303901B1 (en) 1997-05-20 2001-10-16 The Regents Of The University Of California Method to reduce damage to backing plate
US5891192A (en) * 1997-05-22 1999-04-06 The Regents Of The University Of California Ion-implanted protein-coated intralumenal implants
US6056993A (en) 1997-05-30 2000-05-02 Schneider (Usa) Inc. Porous protheses and methods for making the same wherein the protheses are formed by spraying water soluble and water insoluble fibers onto a rotating mandrel
DE19731021A1 (en) 1997-07-18 1999-01-21 Meyer Joerg In vivo degradable metallic implant
US5980928A (en) 1997-07-29 1999-11-09 Terry; Paul B. Implant for preventing conjunctivitis in cattle
US6340367B1 (en) 1997-08-01 2002-01-22 Boston Scientific Scimed, Inc. Radiopaque markers and methods of using the same
US5980564A (en) 1997-08-01 1999-11-09 Schneider (Usa) Inc. Bioabsorbable implantable endoprosthesis with reservoir
US6245103B1 (en) 1997-08-01 2001-06-12 Schneider (Usa) Inc Bioabsorbable self-expanding stent
US6174330B1 (en) 1997-08-01 2001-01-16 Schneider (Usa) Inc Bioabsorbable marker having radiopaque constituents
US6121027A (en) 1997-08-15 2000-09-19 Surmodics, Inc. Polybifunctional reagent having a polymeric backbone and photoreactive moieties and bioactive groups
US6117979A (en) 1997-08-18 2000-09-12 Medtronic, Inc. Process for making a bioprosthetic device and implants produced therefrom
US6129928A (en) 1997-09-05 2000-10-10 Icet, Inc. Biomimetic calcium phosphate implant coatings and methods for making the same
US6284333B1 (en) 1997-09-10 2001-09-04 Scimed Life Systems, Inc. Medical devices made from polymer blends containing low melting temperature liquid crystal polymers
US6010445A (en) * 1997-09-11 2000-01-04 Implant Sciences Corporation Radioactive medical device and process
WO1999016871A2 (en) 1997-09-22 1999-04-08 Max-Planck-Gesellschaft Zur Forderung Der Wissensc Nucleic acid catalysts with endonuclease activity
US5976182A (en) 1997-10-03 1999-11-02 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent and method of loading the same
US6015541A (en) * 1997-11-03 2000-01-18 Micro Therapeutics, Inc. Radioactive embolizing compositions
DE19881727D2 (en) 1997-11-24 2001-01-04 Herbert P Jennissen Process for immobilizing mediator molecules on inorganic and metallic implant materials
US6093463A (en) 1997-12-12 2000-07-25 Intella Interventional Systems, Inc. Medical devices made from improved polymer blends
US5957975A (en) 1997-12-15 1999-09-28 The Cleveland Clinic Foundation Stent having a programmed pattern of in vivo degradation
US6626939B1 (en) 1997-12-18 2003-09-30 Boston Scientific Scimed, Inc. Stent-graft with bioabsorbable structural support
US5986169A (en) 1997-12-31 1999-11-16 Biorthex Inc. Porous nickel-titanium alloy article
WO1999034750A1 (en) * 1998-01-06 1999-07-15 Bioamide, Inc. Bioabsorbable fibers and reinforced composites produced therefrom
US6224626B1 (en) 1998-02-17 2001-05-01 Md3, Inc. Ultra-thin expandable stent
RU2215542C2 (en) 1998-02-23 2003-11-10 Массачусетс Инститьют Оф Текнолоджи Biodecomposing polymers able recovery of form
DK1062278T3 (en) 1998-02-23 2006-09-25 Mnemoscience Gmbh Polymers with shape memory
US5938697A (en) 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US6110188A (en) 1998-03-09 2000-08-29 Corvascular, Inc. Anastomosis method
US6113629A (en) 1998-05-01 2000-09-05 Micrus Corporation Hydrogel for the therapeutic treatment of aneurysms
US6083258A (en) 1998-05-28 2000-07-04 Yadav; Jay S. Locking stent
EP0966979B1 (en) 1998-06-25 2006-03-08 Biotronik AG Implantable bioresorbable support for the vascular walls, in particular coronary stent
DE19856983A1 (en) 1998-06-25 1999-12-30 Biotronik Mess & Therapieg Implantable, bioresorbable vascular wall support, in particular coronary stent
US6153252A (en) 1998-06-30 2000-11-28 Ethicon, Inc. Process for coating stents
WO2000023123A1 (en) 1998-10-19 2000-04-27 Synthes Ag Chur Hardenable ceramic hydraulic cement
DE19855421C2 (en) * 1998-11-02 2001-09-20 Alcove Surfaces Gmbh Implant
DE69822470T2 (en) 1998-11-12 2005-01-20 Takiron Co. Ltd. Biodegradable absorbable shape memory material
US6125523A (en) 1998-11-20 2000-10-03 Advanced Cardiovascular Systems, Inc. Stent crimping tool and method of use
US6350277B1 (en) 1999-01-15 2002-02-26 Scimed Life Systems, Inc. Stents with temporary retaining bands
DE60017363T2 (en) 1999-02-02 2006-03-02 Wright Medical Technology Inc., Arlington CONTROLLED RELEASE OF A COMPOSITE MATERIAL
US6187045B1 (en) 1999-02-10 2001-02-13 Thomas K. Fehring Enhanced biocompatible implants and alloys
EP1156758B1 (en) * 1999-02-26 2008-10-15 LeMaitre Vascular, Inc. Coiled stent
US6183505B1 (en) * 1999-03-11 2001-02-06 Medtronic Ave, Inc. Method of stent retention to a delivery catheter balloon-braided retainers
US6066156A (en) 1999-03-11 2000-05-23 Advanced Cardiovascular Systems, Inc. Temperature activated adhesive for releasably attaching stents to balloons
US6667049B2 (en) 1999-06-14 2003-12-23 Ethicon, Inc. Relic process for producing bioresorbable ceramic tissue scaffolds
US6312459B1 (en) 1999-06-30 2001-11-06 Advanced Cardiovascular Systems, Inc. Stent design for use in small vessels
US6177523B1 (en) * 1999-07-14 2001-01-23 Cardiotech International, Inc. Functionalized polyurethanes
AUPQ170799A0 (en) 1999-07-20 1999-08-12 Cardiac Crc Nominees Pty Limited Shape memory polyurethane or polyurethane-urea polymers
DE19938704C1 (en) * 1999-08-14 2001-10-31 Ivoclar Vivadent Ag Process for the production of reaction systems for implantation in the human and animal body as a bone substitute, which i.a. Contain calcium and phosphorus
US6479565B1 (en) 1999-08-16 2002-11-12 Harold R. Stanley Bioactive ceramic cement
US6379381B1 (en) * 1999-09-03 2002-04-30 Advanced Cardiovascular Systems, Inc. Porous prosthesis and a method of depositing substances into the pores
JP4172883B2 (en) 1999-09-08 2008-10-29 Hoya株式会社 Drug sustained release carrier and method for producing drug sustained release carrier
WO2001026584A1 (en) 1999-10-14 2001-04-19 United Stenting, Inc. Stents with multilayered struts
DE19953771C1 (en) * 1999-11-09 2001-06-13 Coripharm Medizinprodukte Gmbh Absorbable bone implant material and method for producing the same
US7226475B2 (en) 1999-11-09 2007-06-05 Boston Scientific Scimed, Inc. Stent with variable properties
WO2001035928A1 (en) 1999-11-17 2001-05-25 Microchips, Inc. Microfabricated devices for the delivery of molecules into a carrier fluid
US7947069B2 (en) 1999-11-24 2011-05-24 University Of Washington Medical devices comprising small fiber biomaterials, and methods of use
US6554854B1 (en) 1999-12-10 2003-04-29 Scimed Life Systems, Inc. Process for laser joining dissimilar metals and endoluminal stent with radiopaque marker produced thereby
US6338739B1 (en) 1999-12-22 2002-01-15 Ethicon, Inc. Biodegradable stent
US6494908B1 (en) 1999-12-22 2002-12-17 Ethicon, Inc. Removable stent for body lumens
US6981987B2 (en) * 1999-12-22 2006-01-03 Ethicon, Inc. Removable stent for body lumens
US6375826B1 (en) * 2000-02-14 2002-04-23 Advanced Cardiovascular Systems, Inc. Electro-polishing fixture and electrolyte solution for polishing stents and method
KR100371559B1 (en) * 2000-04-03 2003-02-06 주식회사 경원메디칼 Calcium phosphate artificial bone as osteoconductive and biodegradable bone substitute material
US6527801B1 (en) * 2000-04-13 2003-03-04 Advanced Cardiovascular Systems, Inc. Biodegradable drug delivery material for stent
EP1153621A1 (en) 2000-05-12 2001-11-14 MERCK PATENT GmbH Biocements based on a mixture of TCP-PHA with improved compressive strength
US6395326B1 (en) 2000-05-31 2002-05-28 Advanced Cardiovascular Systems, Inc. Apparatus and method for depositing a coating onto a surface of a prosthesis
US6561788B1 (en) * 2000-05-31 2003-05-13 Advanced Cardiovascular Systems, Inc. Modular mold designs
IL137090A (en) 2000-06-29 2010-04-15 Pentech Medical Devices Ltd Polymeric stent
US6569191B1 (en) 2000-07-27 2003-05-27 Bionx Implants, Inc. Self-expanding stent with enhanced radial expansion and shape memory
US6574851B1 (en) 2000-07-31 2003-06-10 Advanced Cardiovascular Systems, Inc. Stent made by rotational molding or centrifugal casting and method for making the same
US6485512B1 (en) 2000-09-27 2002-11-26 Advanced Cardiovascular Systems, Inc. Two-stage light curable stent and delivery system
US6746773B2 (en) 2000-09-29 2004-06-08 Ethicon, Inc. Coatings for medical devices
US20020111590A1 (en) 2000-09-29 2002-08-15 Davila Luis A. Medical devices, drug coatings and methods for maintaining the drug coatings thereon
US6492615B1 (en) 2000-10-12 2002-12-10 Scimed Life Systems, Inc. Laser polishing of medical devices
US7267685B2 (en) * 2000-11-16 2007-09-11 Cordis Corporation Bilateral extension prosthesis and method of delivery
US6517888B1 (en) 2000-11-28 2003-02-11 Scimed Life Systems, Inc. Method for manufacturing a medical device having a coated portion by laser ablation
US6664335B2 (en) 2000-11-30 2003-12-16 Cardiac Pacemakers, Inc. Polyurethane elastomer article with “shape memory” and medical devices therefrom
US6565599B1 (en) 2000-12-28 2003-05-20 Advanced Cardiovascular Systems, Inc. Hybrid stent
US6563080B2 (en) 2001-02-15 2003-05-13 Scimed Life Systems, Inc. Laser cutting of stents and other medical devices
US6540777B2 (en) 2001-02-15 2003-04-01 Scimed Life Systems, Inc. Locking stent
WO2002066096A2 (en) * 2001-02-16 2002-08-29 Cordis Corporation Balloon catheter stent delivery system with ridges
US8262687B2 (en) * 2001-02-27 2012-09-11 Kyoto Medical Planning Co., Ltd. Stent holding member and stent feeding system
US6764505B1 (en) 2001-04-12 2004-07-20 Advanced Cardiovascular Systems, Inc. Variable surface area stent
US6679980B1 (en) * 2001-06-13 2004-01-20 Advanced Cardiovascular Systems, Inc. Apparatus for electropolishing a stent
US6695920B1 (en) * 2001-06-27 2004-02-24 Advanced Cardiovascular Systems, Inc. Mandrel for supporting a stent and a method of using the mandrel to coat a stent
US6585755B2 (en) 2001-06-29 2003-07-01 Advanced Cardiovascular Polymeric stent suitable for imaging by MRI and fluoroscopy
JP2005503865A (en) 2001-09-28 2005-02-10 ボストン サイエンティフィック リミテッド Medical device comprising nanomaterial and treatment method using the same
CA2464053A1 (en) * 2001-11-09 2003-05-22 Novoste Corporation Baloon catheter with non-deployable stent
US20030105530A1 (en) 2001-12-04 2003-06-05 Inion Ltd. Biodegradable implant and method for manufacturing one
US6752826B2 (en) 2001-12-14 2004-06-22 Thoratec Corporation Layered stent-graft and methods of making the same
US20030187495A1 (en) 2002-04-01 2003-10-02 Cully Edward H. Endoluminal devices, embolic filters, methods of manufacture and use
US7270675B2 (en) 2002-05-10 2007-09-18 Cordis Corporation Method of forming a tubular membrane on a structural frame
US20030236565A1 (en) 2002-06-21 2003-12-25 Dimatteo Kristian Implantable prosthesis
US7141063B2 (en) 2002-08-06 2006-11-28 Icon Medical Corp. Stent with micro-latching hinge joints
US6818063B1 (en) 2002-09-24 2004-11-16 Advanced Cardiovascular Systems, Inc. Stent mandrel fixture and method for minimizing coating defects
US7455687B2 (en) 2002-12-30 2008-11-25 Advanced Cardiovascular Systems, Inc. Polymer link hybrid stent
US20040143317A1 (en) 2003-01-17 2004-07-22 Stinson Jonathan S. Medical devices
US20040167610A1 (en) 2003-02-26 2004-08-26 Fleming James A. Locking stent
US7025779B2 (en) * 2003-02-26 2006-04-11 Scimed Life Systems, Inc. Endoluminal device having enhanced affixation characteristics
US6846323B2 (en) * 2003-05-15 2005-01-25 Advanced Cardiovascular Systems, Inc. Intravascular stent
IES20030539A2 (en) * 2003-07-22 2005-05-18 Medtronic Vascular Connaught Stents and stent delivery system

Patent Citations (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4130617A (en) * 1977-12-30 1978-12-19 Airco, Inc. Method of making endotracheal tube cuffs
US4264294A (en) * 1979-01-08 1981-04-28 Ruiz Oscar F Profiling die
US6290485B1 (en) * 1995-03-02 2001-09-18 Lixiao Wang Mold for forming a balloon catheter having stepped compliance curve
US5630830A (en) * 1996-04-10 1997-05-20 Medtronic, Inc. Device and method for mounting stents on delivery systems
US5672169A (en) * 1996-04-10 1997-09-30 Medtronic, Inc. Stent mounting device
US5653691A (en) * 1996-04-25 1997-08-05 Rupp; Garry Eugene Thickened inner lumen for uniform stent expansion and method of making
US5759474A (en) * 1996-04-25 1998-06-02 Medtronic, Inc. Method of making thickened inner lumen for uniform stent expansion
US6676697B1 (en) * 1996-09-19 2004-01-13 Medinol Ltd. Stent with variable features to optimize support and method of making such stent
US20020099406A1 (en) * 1997-05-22 2002-07-25 St. Germain Jon P. Variable expansion force stent
US6464720B2 (en) * 1997-09-24 2002-10-15 Cook Incorporated Radially expandable stent
US6911041B1 (en) * 1997-10-23 2005-06-28 C. R. Bard, Inc. Expanded stent and a method for producing same
US6569193B1 (en) * 1999-07-22 2003-05-27 Advanced Cardiovascular Systems, Inc. Tapered self-expanding stent
US6540774B1 (en) * 1999-08-31 2003-04-01 Advanced Cardiovascular Systems, Inc. Stent design with end rings having enhanced strength and radiopacity
US6387117B1 (en) * 1999-09-22 2002-05-14 Scimed Life Systems, Inc. Stent crimping system
US6481262B2 (en) * 1999-12-30 2002-11-19 Advanced Cardiovascular Systems, Inc. Stent crimping tool
US7097440B2 (en) * 2000-07-14 2006-08-29 Advanced Cardiovascular Systems, Inc. Embolic protection systems
US6726713B2 (en) * 2000-08-09 2004-04-27 Biotronik Mess- Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin Method and device for crimping a stent
JP2002233579A (en) * 2000-12-04 2002-08-20 Piolax Medical Device:Kk Method of manufacturing for metallic stent
US20020077690A1 (en) * 2000-12-18 2002-06-20 Lixiao Wang Catheter for controlled stent delivery
US6776604B1 (en) * 2001-12-20 2004-08-17 Trivascular, Inc. Method and apparatus for shape forming endovascular graft material
US6948223B2 (en) * 2002-05-03 2005-09-27 Medtronic Vascular, Inc. Apparatus for mounting a stent onto a stent delivery system
US20040249435A1 (en) * 2003-06-09 2004-12-09 Xtent, Inc. Stent deployment systems and methods
US7055237B2 (en) * 2003-09-29 2006-06-06 Medtronic Vascular, Inc. Method of forming a drug eluting stent
US20080208254A1 (en) * 2005-07-06 2008-08-28 Steffen Berger Sucking and Chewing Article for Babies or Small Children

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20220354631A1 (en) * 2018-11-19 2022-11-10 Pulmair Medical, Inc. Implantable Artificial Bronchus
US11654010B2 (en) * 2018-11-19 2023-05-23 Pulmair Medical, Inc. Implantable artificial bronchus

Also Published As

Publication number Publication date
WO2006110474A3 (en) 2007-04-12
US7381048B2 (en) 2008-06-03
US20080254159A1 (en) 2008-10-16
US20060229695A1 (en) 2006-10-12
WO2006110474A2 (en) 2006-10-19
EP1874230A2 (en) 2008-01-09
US8393887B2 (en) 2013-03-12
US20130197620A1 (en) 2013-08-01
JP2008535627A (en) 2008-09-04
US7708548B2 (en) 2010-05-04

Similar Documents

Publication Publication Date Title
US8393887B2 (en) Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US7886419B2 (en) Stent crimping apparatus and method
US10357384B2 (en) Radially expandable polymer prosthesis and method of making same
US8002817B2 (en) Stents with high radial strength and methods of manufacturing same
US8323329B2 (en) Stents with enhanced fracture toughness
US20070282433A1 (en) Stent with retention protrusions formed during crimping
US8940037B2 (en) Stent having circumferentially deformable struts
US9192494B2 (en) Locking polymer stents
US8377533B2 (en) Bioabsorbable stent with layers having different degradation rates
US9439788B2 (en) Stent locking element and a method of securing a stent on a delivery system
US8112874B2 (en) Stent island removal system

Legal Events

Date Code Title Description
REMI Maintenance fee reminder mailed
LAPS Lapse for failure to pay maintenance fees
STCH Information on status: patent discontinuation

Free format text: PATENT EXPIRED DUE TO NONPAYMENT OF MAINTENANCE FEES UNDER 37 CFR 1.362

FP Lapsed due to failure to pay maintenance fee

Effective date: 20170312